EP2789314A2 - Système de remplacement valvulaire minimalement invasif - Google Patents

Système de remplacement valvulaire minimalement invasif Download PDF

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Publication number
EP2789314A2
EP2789314A2 EP20140163073 EP14163073A EP2789314A2 EP 2789314 A2 EP2789314 A2 EP 2789314A2 EP 20140163073 EP20140163073 EP 20140163073 EP 14163073 A EP14163073 A EP 14163073A EP 2789314 A2 EP2789314 A2 EP 2789314A2
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EP
European Patent Office
Prior art keywords
valve
anchoring structure
inflow
rim
outflow
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP20140163073
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German (de)
English (en)
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EP2789314A3 (fr
EP2789314B1 (fr
Inventor
Keith E. Myers
Tuor Tan Nguyen
Jason Artof
Douglas S Cali
Brian Biancucci
Oleg Svanidze
Bjarne Bergheim
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Medtronic 3F Therapeutics Inc
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3F Therapeutics Inc
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Application filed by 3F Therapeutics Inc filed Critical 3F Therapeutics Inc
Priority claimed from EP04794398.0A external-priority patent/EP1684671B1/fr
Publication of EP2789314A2 publication Critical patent/EP2789314A2/fr
Publication of EP2789314A3 publication Critical patent/EP2789314A3/fr
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2412Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
    • A61F2/2418Scaffolds therefor, e.g. support stents
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/01Filters implantable into blood vessels
    • A61F2/013Distal protection devices, i.e. devices placed distally in combination with another endovascular procedure, e.g. angioplasty or stenting
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2427Devices for manipulating or deploying heart valves during implantation
    • A61F2/243Deployment by mechanical expansion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2427Devices for manipulating or deploying heart valves during implantation
    • A61F2/2439Expansion controlled by filaments
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2496Devices for determining the dimensions of the prosthetic valve to be implanted, e.g. templates, sizers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A61F2210/0019Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at only one temperature whilst inside or touching the human body, e.g. constrained in a non-operative shape during surgery, another temperature only occurring before the operation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A61F2210/0023Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at different temperatures whilst inside or touching the human body, heated or cooled by external energy source or cold supply
    • A61F2210/0028Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at different temperatures whilst inside or touching the human body, heated or cooled by external energy source or cold supply cooled
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0008Fixation appliances for connecting prostheses to the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0008Fixation appliances for connecting prostheses to the body
    • A61F2220/0016Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/005Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using adhesives
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0066Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements stapled
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0075Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0028Shapes in the form of latin or greek characters
    • A61F2230/0054V-shaped
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0059Additional features; Implant or prostheses properties not otherwise provided for temporary

Definitions

  • the present invention relates to devices and systems for the replacement of physiological valves.
  • valves The transport of vital fluids in the human body is largely regulated by valves.
  • Physiological valves are designed to prevent the backflow of bodily fluids, such as blood, lymph, urine, bile, etc., thereby keeping the body's fluid dynamics unidirectional for proper homeostasis.
  • bodily fluids such as blood, lymph, urine, bile, etc.
  • venous valves maintain the upward flow of blood, particularly from the lower extremities, back toward the heart
  • lymphatic valves prevent the backflow of lymph within the lymph vessels, particularly those of the limbs.
  • valves Because of their common function, valves share certain anatomical features despite variations in relative size.
  • the cardiac valves are among the largest valves in the body with diameters that may exceed 30 mm, while valves of the smaller veins may have diameters no larger than a fraction of a millimeter. Regardless of their size, however, many physiological valves are situated in specialized anatomical structures known as sinuses.
  • Valve sinuses can be described as dilations or bulges in the vessel wall that houses the valve.
  • the geometry of the sinus has a function in the operation and fluid dynamics of the valve. One function is to guide fluid flow so as to create eddy currents that prevent the valve leaflets from adhering to the wall of the vessel at the peak of flow velocity, such as during systole.
  • Another function of the sinus geometry is to generate currents that facilitate the precise closing of the leaflets at the beginning of backflow pressure.
  • the sinus geometry is also important in reducing the stress exerted by differential fluid flow pressure on the valve leaflets or
  • the eddy currents occurring within the sinuses of Valsalva in the natural aortic root have been shown to be important in creating smooth, gradual and gentle closure of the aortic valve at the end of systole. Blood is permitted to travel along the curved contour of the sinus and onto the valve leaflets to effect their closure, thereby reducing the pressure that would otherwise be exerted by direct fluid flow onto the valve leaflets.
  • the sinuses of Valsalva also contain the coronary ostia, which are outflow openings of the arteries that feed the heart muscle. When valve sinuses contain such outflow openings, they serve the additional purpose of providing blood flow to such vessels throughout the cardiac cycle.
  • valves When valves exhibit abnormal anatomy and function as a result of valve disease or injury, the unidirectional flow of the physiological fluid they are designed to regulate is disrupted, resulting in increased hydrostatic pressure.
  • venous valvular dysfunction leads to blood flowing back and pooling in the lower legs, resulting in pain, swelling and edema, changes in skin color, and skin ulcerations that can be extremely difficult to treat. Lymphatic valve insufficiency can result in lymphedema with tissue fibrosis and gross distention of the affected body part.
  • Cardiac valvular disease may lead to pulmonary hypertension and edema, atrial fibrillation, and right heart failure in the case of mitral and tricuspid valve stenosis; or pulmonary congestion, left ventricular contractile impairment and congestive heart failure in the case of mitral regurgitation and aortic stenosis.
  • all valvular diseases result in either stenosis, in which the valve does not open properly, impeding fluid flow across it and causing a rise in fluid pressure, or insufficiency/regurgitation, in which the valve does not close properly and the fluid leaks back across the valve, creating backflow.
  • Some valves are afflicted with both stenosis and insufficiency, in which case the valve neither opens fully nor closes completely.
  • valve replacement surgery is becoming a widely used medical procedure, described and illustrated in numerous books and articles.
  • the diseased or abnormal valve is typically cut out and replaced with either a mechanical or tissue valve.
  • a conventional heart valve replacement surgery involves accessing the heart in a patient's thoracic cavity through a longitudinal incision in the chest. For example, a median sternotomy requires cutting through the sternum and forcing the two opposite halves of the rib cage to be spread apart, allowing access to the thoracic cavity and the heart within. The patient is then placed on cardiopulmonary bypass, which involves stopping the heart to permit access to the internal chambers.
  • Such open heart surgery is particularly invasive and involves a lengthy and difficult recovery period. Reducing or eliminating the time a patient spends in surgery is thus a goal of foremost clinical priority.
  • valve assemblies that allow implantation with minimal or no sutures would be greatly advantageous.
  • devices have been developed for the endovascular implantation of replacement valves, including collapsing, delivering, and then expanding the valve, such devices do not configure the valve in a manner that takes advantage of the natural compartments formed by the valve sinuses for optimal fluid dynamics and valve performance.
  • such valve constructs are configured such that the tissue leaflets of the support valve come into contact with the support structure, either during the collapsed or expanded state, or both.
  • Such contact is capable of contributing undesired stress on the valve leaflet.
  • support structures are not configured to properly support a tissue valve having a scalloped inflow annulus such as that disclosed in the U.S. patent application serial number 09/772,526 which is incorporated by reference herein in its entirety.
  • a valve replacement system comprising a collapsible and expandable valve assembly that is capable of being secured into position with minimal or no suturing; facilitating an anatomically optimal position of the valve; maintaining an open pathway for other vessel openings of vessels that may be located in the valvular sinuses; and minimizing or reducing stress to the tissue valve leaflets.
  • the valves of the present invention may comprise a plurality of joined leaflets with a corresponding number of commissural tabs. Generally, however, the desired valve will contain two to four leaflets and commissural tabs. Examples of other suitable valves are disclosed in U.S.
  • the present invention provides systems and devices for the replacement of physiological valves.
  • the replacement valve assemblies are adapted to fit substantially within the valve sinuses. Because the devices and procedures provided by the present invention eliminate or reduce the need for suturing, time spent in surgery is significantly decreased, and the risks associated with surgery are minimized. Further, the devices of the present invention are suitable for delivery by cannula or catheter.
  • a valve anchoring structure is provided that is dimensioned to be placed substantially within the valve sinus.
  • the valve anchoring structure extends substantially across the length of the valve sinus region.
  • a valve assembly comprising a valve and anchoring structure, in which the valve comprises a body having a proximal end and a distal end, an inlet at the proximal end, and an outlet at the distal end.
  • the inlet comprises an inflow annulus, preferably with either a scalloped or straight edge.
  • the outlet comprises a plurality of tabs that are supported by the anchoring means at the distal end. In preferred embodiments of the invention, the plurality of tabs are spaced evenly around the circumference of the valve.
  • a valve assembly is provided in which there is minimal or no contact between the valve and anchoring structure.
  • a valve assembly in which the valve is capable of achieving full opening and full closure without contacting the anchoring structure.
  • a valve assembly in which the vertical components of the anchoring structure are limited to the commissural posts between sinus cavities, thereby minimizing contact between mechanical components and fluid, as well as providing flow to vessels located in the valve sinus.
  • a valve is provided that firmly attaches to the valve sinus, obviating the need for suturing to secure the valve placement.
  • a valve assembly in which the anchoring structure may be collapsed to at least fifty percent of its maximum diameter.
  • an expansion and contraction device is provided to facilitate implantation of the valve and anchoring structure.
  • the present invention provides adhesive means for securing the valve assembly in a valve sinus.
  • a valve sizing apparatus for the noninvasive determination of native valve size.
  • the present invention also provides cutting means to remove the native diseased valve.
  • One aspect of the cutting means comprises a plurality of jaw elements, each jaw element having a sharp end enabling the jaw element to cut through at least a portion of the native valve.
  • Another aspect of the cutting means comprises a plurality of electrode elements, wherein radiofrequency energy is delivered to each electrode element enabling the electrode element to cut through at least a portion of the native valve.
  • a further aspect of the cutting means comprises a plurality of ultrasound transducer elements, wherein ultrasound energy is delivered to each transducer element enabling the transducer element to cut through at least a portion of the native valve.
  • the present invention provides a temporary two-way valve and distal protection filter assembly.
  • methods and assemblies for the expansion and placement of replacement valves are provided using an inflatable perfusion balloon.
  • the inflatable perfusion balloon permits continued blood flow therethrough even while it is in an inflated and/or fully expanded state.
  • a valve (1) comprises a distal or outflow end (2), leaflets (3) and a proximal or inflow end (4).
  • a typical valve functions similar to a collapsible tube in that it opens widely during systole or in response to muscular contraction, to enable unobstructed forward flow across the valvular orifice ( Figure 1 A) .
  • Figure 1B At the end of systole or contraction, as illustrated in Figure 1B , as forward flow decelerates, the walls of the tube are forced centrally between the sites of attachment to the vessel wall and the valve closes completely.
  • a preferred valve (5) for use with the systems and devices of the present invention is illustrated in Figure 2 and is comprised of a body having a proximal end or inflow ring (6) and a distal end or outflow ring (7).
  • the body is comprised of multiple leaflets of valve tissue joined by seams (8), wherein each seam is formed by a junction of two leaflets.
  • a commissural tab region (9) extends from each seam at the distal end of the valve body.
  • the proximal end (6) has an inflow ring with a peripheral edge that can be scalloped or straight.
  • the inflow ring (6) of the valve can further comprise a reinforcement structure (10) that can be stitched to it. In preferred embodiments of the invention, the inflow edge of the valve is scalloped.
  • valve sinuses are dilations of the vessel wall that surround the natural valve leaflets.
  • each natural valve leaflet has a separate sinus bulge or cavity that allows for maximal opening of the leaflet at peak flow without permitting contact between the leaflet and the vessel wall.
  • a two-leaflet valve is surrounded by two sinus bulges, a three-leaflet valve by three, and a four-leaflet valve by four sinus cavities.
  • the individual sinus bulges or cavities are separated by vertical fibrous structures known as commissural posts.
  • FIGs 3A and B illustrate the reduced curvature of the commissural posts (11) compared with the curvature of the sinus cavities (12).
  • Figure 3C shows a view from outside the vessel of a commissural post (11) between two sinus cavities (12), while Figure 3A shows a cross sectional view from the top of a closed valve within a valve sinus.
  • the areas between the bulges define the commissural posts (11) and as can be clearly seen in Figure 3B , the commissural posts serve as the sites of attachment for the valve leaflets to the vessel wall (13).
  • Figures 3B and C also show the narrowing diameter of the sinus region at both its inflow end (14) and outflow end (15) to form the inflow and outflow annuli of the sinus region.
  • the valve sinuses form a natural compartment to support the operation of the valve by preventing contact between the leaflets and the vessel wall, which, in turn, may lead to adherence of the leaflets and/or result in detrimental wear and tear of the leaflets.
  • the valve sinuses are also designed to share the stress conditions imposed on the valve leaflets during closure when fluid pressure on the closed leaflets is greatest.
  • the valve sinuses further create favorable fluid dynamics through currents that soften an otherwise abrupt closure of the leaflets under conditions of high backflow pressure.
  • the sinuses ensure constant flow to any vessels located within the sinus cavities.
  • the valve sinus region is characterized by certain relative dimensions which remain constant regardless of the actual size of the sinuses.
  • the diameter of the sinus is at its largest at the center of the cavities or bulges (16), while there is pronounced narrowing of the sinus region at both the inflow annulus (17) and outflow annulus (18).
  • the height of the sinus (19) i.e. the distance between the inflow and outflow annuli remains proportional to its overall dimensions. It is thus apparent that the sinus region forms an anatomical compartment with certain constant features that are uniquely adapted to house a valve.
  • the systems and devices of the present invention are designed to utilize these anatomical features of the native sinus region for optimal replacement valve function and position.
  • the replacement valve assembly comprises a collapsible and expandable anchoring structure adapted to support a valve distally along the commissural tab region and proximally along the inflow annulus.
  • Figure 5 shows a preferred anchoring structure adapted to support a valve such as that illustrated in Figure 2 .
  • the preferred anchoring structure has a generally tubular configuration within which the valve Is secured.
  • the valve is secured at its proximal (inflow) annulus by attachment to the inflow rim (20) of the anchoring structure and at its distal end via the commissural tabs that are threaded through the axially extending slots (21), which are formed in the support posts (22) that extend longitudinally from the inflow rim (20) to the outflow rim (23) of the anchoring structure.
  • the distal ends (24) of the support posts contact the outflow rim (23) of the anchoring structure
  • the proximal ends (25) of the support posts contact the inflow rim (20) of the anchoring structure.
  • the outflow rim (23) of the anchoring structure is depicted as comprising a plurality of rings that extend between the support posts (22) generally at or above the axially extending slots (21) that reside therein.
  • the plurality of rings of the outflow rim (23) are configured in an undulating or zigzag pattern forming peaks (26) and valleys (27), wherein the individual rings remain substantially parallel to one another.
  • the plurality of rings of the outflow rim comprise a vertical connector element (28) positioned at the center of the valleys (27) formed by the undulating or zigzag pattern. This vertical connector element (28) is designed to stabilize the anchoring structure and to prevent distortion of the valve during compression and expansion of the anchoring structure comprising the valve.
  • the vertical element (28) extends longitudinally in the axial direction of the cylindrical anchoring structure.
  • the outflow rim (23) of the anchoring structure comprises two rings.
  • the inflow rim (20) of the support structure comprises a single ring that extends between the support posts (22).
  • Both the inflow (20) and outflow (23) rims of the anchoring structure are formed with an undulating or zigzag configuration, although the inflow rim (20) may have a shorter wavelength (circumferential dimension from peak to peak) and a lesser wave height (axial dimension from peak to peak) than the outflow rim (23).
  • the wavelengths and wave heights of the inflow (20) and outflow (23) rims are selected to ensure uniform compression and expansion of the anchoring structure without distortion.
  • the wavelength of the inflow rim (20) is further selected to support the geometry of the scalloped inflow annulus of a preferred valve of the present invention.
  • the undulating or zigzag pattern that forms the inflow rim (20) of the anchoring structure is configured such that the proximal ends (25) of the vertical support posts (22) are connected to the peaks (29) of the inflow rim (20).
  • the undulating or zigzag pattern that forms the outflow rim (23) of the anchoring structure is configured such that the distal ends (24) of the support posts (22) are connected to the valleys (27) of the outflow rim (23).
  • Locating the distal ends (24) of the support posts at the valleys (27) of the outflow rim (23) will prevent the longitudinal extension of outflow rim (23) in the direction of the valve secured within the lumen of the anchoring structure upon compression of the valve assembly, thereby eliminating any contact between valve and anchoring structure.
  • Locating the proximal ends (25) of the support posts at the peaks (29) of the inflow rim (20) will prevent longitudinal extension of the inflow rim (20) in the direction of the valve tissue.
  • Figure 5 further shows that the support posts (22) are configured generally in the shape of paddle with the axial slot (21) extending internally within the blade (30) of the paddle.
  • the blade (30) of the paddle is oriented toward the outflow rim (23) of the anchoring structure and connects to the outflow rim (23) at a valley (27) of the undulating or zigzag pattern of the outflow rim (23).
  • An important function of the support posts (22) is the stabilization of the valve in general, and in particular the prevention of any longitudinal extension at points of valve attachment to preclude valve stretching or distortion upon compression of the device.
  • the blades (30) of the paddle-shaped support posts (22) are designed to accommodate the commissural tabs of the valve.
  • the support posts (22) further comprise triangular shaped elements (31) extending on each side of the proximal end (25) of the support post.
  • the triangular shaped elements (31) are designed to serve as attachments sites for the sewing cuff gasket and may be designed in different shapes without losing their function.
  • the number of support posts (22) in this preferred embodiment can range from two to four, depending on the number of commissural posts present in the valve sinus.
  • the anchoring structure comprises three support posts for a three-leaflet valve with a sinus that features three natural commissural posts.
  • the support posts (22) of the anchoring structure are configured to coincide with the natural commissural posts of the sinus.
  • FIGs 6A and B show the preferred embodiment of Figure 5 having a valve secured internally.
  • the valve (32) is secured at its proximal (inflow) annulus (33) by attachment to the inflow rim (20) of the anchoring structure and at its outflow or distal end (34) via the commissural tabs (35) that are threaded through the axially extending slots (21), which are formed in the support posts (22) that extend longitudinally from the inflow rim (20) to the outflow rim (23) of the anchoring structure.
  • the outflow rim (23) of the anchoring structure is configured to be longitudinally displaced from the distal outflow annulus (34) of the valve leaflets (36) that reside within the lumen of the tubular anchoring structure, thereby avoiding any contact between the valve leaflets (36) and the anchoring structure.
  • the inflow rim (20) of the anchoring structure can be secured to the proximal inflow annulus (33) of the valve via a suitable fabric that may be wrapped around the circumferential juncture at the inflow end (33) and stitched into position to form a sewing cuff (37).
  • the fabric may be made of any suitable material including but not limited to woven polyester, such as polyethylene terepthalate, polytetrafluoroethylene (PTFE), or other biocompatible material.
  • the valve (32) is secured inside the anchoring structure by sewing a fabric ring (37) around the inflow rim (20) of the anchoring structure so as to create a sealing surface around the outer perimeter of valve's inflow annulus (33).
  • the fabric ring (37) comprises two sewing cuff rings as shown in Figures 6A and B , with the second sewing cuff ring (38) having a larger diameter than the inflow annulus of the native valve sinus to ensure the firm lodging of the anchoring structure against the inflow annulus of the native valve sinus, thereby creating a tight, gasket-like seal.
  • valve (32) internally to the preferred anchoring structure with only the fabric of the commissural mounting tabs (35) of the valve (32) contacting the support posts (22) at the distal outflow annulus of the valve (34), while the proximal inflow annulus (33) of the valve is separated from the inflow rim (20) of the anchoring structure by the sewing cloth (37), ensures that no part of the valve (32) is contacted by the anchoring structure during operation of the valve (32), thereby eliminating wear on the valve (32) that may be occasioned by contact with mechanical elements.
  • the outflow rim (23) of the anchoring structure is depicted as comprising a plurality of rings that extend between the support posts (22) generally at or above the axially extending slots (21) that reside at their distal ends (24).
  • the plurality of rings of the outflow rim (23) are configured in an undulating or zigzag pattern forming peaks (26) and valleys (27), wherein the individual rings remain substantially parallel to one another.
  • the plurality of rings of the outflow rim comprise a vertical connector element (28) positioned at the center of the valleys (27) formed by the undulating or zigzag pattern.
  • This vertical connector element (28) is designed to stabilize the anchoring structure and to prevent distortion of the valve during compression and expansion of the anchoring structure containing the valve within.
  • the vertical element (28) extends longitudinally in the axial direction of the cylindrical anchoring structure.
  • the outflow rim of the anchoring structure comprises two rings.
  • Figure 6 C shows another implementation of a preferred anchoring structure of the present invention.
  • the implementation shown in Figure 6 C features an inflow rim (20) comprising two rings that are substantially parallel to each other and are connected by a vertical connector element (39) positioned at the center of the peaks (29) formed by the undulating or zigzag pattern.
  • This vertical connector element (39) is designed to stabilize the anchoring structure and to prevent distortion of the valve during compression and expansion of the anchoring structure comprising the valve.
  • the vertical element (39) extends longitudinally in the axial direction of the cylindrical anchoring structure.
  • Figure 6 C also shows that the distal end (24) of the support post (22) may further comprise suture bores (41) to facilitate the placement of additional sutures for the securing the valve to the anchoring structure.
  • the wavelengths and wave heights of the inflow (20) and outflow rims (23) are selected to ensure uniform compression and expansion of the anchoring structure without distortion, a different wavelength and height may be chosen for the inflow ring (20) of an implementation of a preferred embodiment of an anchoring structure featuring an inflow rim (20) with two substantially parallel undulating rings as shown in Figure 6 C .
  • the inflow rim (20) depicted in Figure 6 C may have substantially the same wavelength and height as the outflow rim (23).
  • the support posts (22) may be modified to comprise a widened proximal end (25) with an axial slot (40) extending longitudinally from the inflow rim (20) toward the distal end (24) of the support posts (22) and centrally through the triangular shaped elements (31).
  • the widening of the proximal end (25) of the support posts (22) protects the triangular shaped elements (31) from distortion by the different collapsed profile of the inflow rim (20) with larger wavelength and height and ensures that no part of the valve (32) will be contacted by the anchoring structure during compression.
  • Figures 7 and 8 show the expansion ( Figure 7 ) and compression ( Figure 8 ) profile of a preferred anchoring structure of the present invention.
  • the anchoring structure is collapsible to at least 50% of its expanded diameter.
  • the undulating or zigzag pattern that forms the inflow rim (20) of the anchoring structure is configured such that the proximal ends (25) of the vertical support posts (22) are connected to the peaks (29) of the inflow rim (20).
  • the undulating or zigzag pattern that forms the outflow rim (23) of the anchoring structure is configured such that the support posts (22) are connected to the valleys (27) of the outflow rim (23).
  • Locating the distal ends (24) of the support posts (22) at the valleys (27) of the outflow rim (23) will prevent the longitudinal extension of outflow rim (23) in the direction of the valve upon compression of the device, thereby eliminating any contact between valve and anchoring structure.
  • locating the proximal ends (25) of the support posts (22) at the peaks (29) of the inflow rim (20) prevents structural interference between the proximal ends (25) of the support posts (22), in particular the triangular shaped elements (31) designed to support the scalloped inflow annulus of the replacement valve, and the undulating pattern of the inflow rim (20), as well as longitudinal extension of the inflow rim (20) in the direction of the valve tissue.
  • compression of the valve and anchoring structure does not lead to distortion of or injury to the valve.
  • Figure 8 shows that the support posts (22) connect to the outflow rim (23) at a valley (27) of the undulating or zigzag pattern and that during compression, the support posts stabilize the anchoring structure by preventing any longitudinal extension at points of valve attachment, that is at the proximal (25) and distal (24) ends of the support posts.
  • the commissural mounting tabs of the valve are attached to the anchoring structure by extending through the axial slots (40) of the support posts to the exterior of the anchoring structure, while the inflow annulus of the valve is connected to the inflow rim (20) of the anchoring structure via a fabric ring.
  • the number of support posts (22) in this preferred embodiment can range from two to four, depending on the number of commissural posts present in the valve sinus.
  • the anchoring structure comprises three support posts (22) for a three-leaflet valve with a sinus that features three natural commissural posts.
  • the support posts (22) of the anchoring structure are configured to coincide with the natural commissural posts of the sinus.
  • an advantage of this arrangement is the additional option for the surgeon of suturing the valve assembly into place, wherein the anchoring structure provides the surgeon with additional guidance as to the proper anatomical positioning of the valve inside the native valve sinuses. Since the anchoring structure is dimensioned to fit precisely into the valve sinus cavities, the surgeon's positioning task is simplified to a visual determination of the location of the commissural posts of the native sinuses and their alignment with the support posts (22) of the anchoring structure of the valve. Thus, the present preferred embodiment takes advantage of the natural features of the valve sinus for the rapid orientation and attachment of the valve assembly. The ability of the anchoring structure to emulate the architecture of the valve sinus thus significantly reduces the surgeon's time spent on suturing the valve into position, should he so desire.
  • the geometry of the preferred embodiment of a valve anchoring structure further naturally positions it across the entire longitudinal extension of the native valve sinus, lodging the anchoring structure firmly against the vessel walls.
  • the inflow rim (20) of the anchoring structure naturally fits into the native valve sinus at a position near the inflow narrowing (annulus) of the native valve sinus against which it is designed to rest, while distally, the outflow rim (23) of the anchoring structure fits into the sinus at a position near the outflow narrowing (annulus) of the sinus against which it is designed to rest.
  • a further advantage of this preferred embodiment of the present invention is the ability of the anchoring structure to emulate the natural compartment formed by the sinus for anchoring the valve.
  • the anchoring structure is able to extend completely across the sinuses without placing mechanical elements into the path of fluid flow and without obstructing flow to any vessel openings that may be present in the valve sinuses.
  • the anchoring structure exerts radial force against the vessel wall so as to produce a compression fit. This may be accomplished by oversizing the anchoring structure such that it permanently seeks to expand to its original size.
  • both the inflow (20) and outflow (23) rims are designed to push radially against the sinus walls near the inflow and outflow annuli of the sinus.
  • the undulating or zigzag pattern formed by the inflow (20) and outflow (23) rings further serves to provide tire-like traction against the sinus wall for anchoring.
  • the combination of compression fit, traction and sewing cuff rings (37 and 38) of the anchoring structure provides a firm anchor for the replacement valve and an optimal configuration in the native valve sinus.
  • the anchoring structure comprises a material that is expandable from a compressed configuration illustrated in Figure 8 into the configuration depicted in Figure 7 .
  • the anchoring structure may be non-self expanding, i.e. capable of being expanded from a compressed state using mechanical means, such as a balloon inflated from within the radial center of the anchoring structure, or using the expansion and compression devices disclosed herein.
  • the anchoring structure comprises vertical tab support posts (22) which are designed to prevent inelastic deformation when the anchoring structure is collapsed prior to implantation.
  • Figure 9 shows a representative flat valve leaflet (36) before it is sewn together with a desired number of additional leaflets (36) to form a three-dimensional replacement valve.
  • the flat pattern of the leaflet (36) can be used to dimension the anchoring structure shown in Figure 10 such that the commissural tabs (35) of the valve (36) will coincide with the axial slots (21) at the distal ends (24) of the support posts (22) and the proximal edges (42) at which the leaflets will be stitched or otherwise attached to each other to form the inflow annulus of the valve can be attached to the proximal ends (25) of the support posts (22) of the anchoring structure via the triangular shaped elements (31).
  • Figures 9 and 10 also show how an anchoring structure and valve may be scaled to fit different sizes of valve sinuses while retaining the proportional dimensions of the valve sinus. For example, if the width (43) of the leaflet (36) shown in Figure 9 is chosen for a certain valve size, then the distance (44) between support posts (22) of the anchoring structure shown in Figure 10 will be determined accordingly. Likewise, the height (45) of the leaflet (36) in Figure 9 will determine the length (46) of the support posts (22) of the anchoring structure in Figure 10 . In this manner, a person of skill in the art can dimension both the valve and anchoring structure to fit any size of valve sinus.
  • FIG. 11 and 12 Another preferred embodiment of the present invention, illustrated in Figures 11 and 12 , comprises a valve supported by a flared anchoring structure.
  • the flared anchoring structure preferably comprises flared-out sections located at both the inflow (47) and outflow rims (48) to anchor it firmly against the narrowed inflow and outflow annuli of the valve sinuses.
  • the flared distal end (48) of the anchoring structure is adapted to support the tab regions of the valve while the flared proximal end (47) supports the valve inflow annulus (33).
  • the flared-out feature prevents contact between the valve tissue and the anchoring structure if the outflow rim (48) is positioned below the upper edges of the valve leaflets (36) in the open position, while also allowing the anchoring structure to secure itself in a sinus cavity of the vascular passageway.
  • the outflow rim (48) of the anchoring structure is comprised of diamond (49) and hexagon (50) shaped structures which facilitate collapsibility and dynamic compliance.
  • the commissural tabs (35) of the valve (32) can be stitched directly to the hexagon shaped elements (50) of the outflow ring, rather than being secured via slots.
  • the flared inflow rim (47) of the anchoring structure preferably comprises a single ring In the form of an undulating or zigzag pattern to which the valve's fabric ring (37) can be sewn.
  • the inflow ring (47) of the anchoring structure is connected to the outflow rim (48) through vertical elements (51) that are positioned to coincide with the commissural posts of the native sinus region.
  • the exemplary embodiment of Figures 11 and 12 comprises three vertical connecting elements (51) for a three-leaflet valve (32).
  • the number of vertical connecting elements (51) is meant to be adapted to the number of native commissural posts present in the particular sinus region.
  • the area between vertical connector elements (51) is thus left free of any structural elements for the accommodation of vessel openings that may be present in the particular valve sinus.
  • a valve is supported by an anchoring structure comprising a plurality of posts (52) with a single ring (53) at the inflow rim.
  • the ring (53) is configured in an undulating or zigzag pattern.
  • the plurality of posts (52) number three for a three-leaflet valve sinus region.
  • the three posts (52) extend in the distal direction from the single ring (53) located at the inflow end of the anchoring structure.
  • the proximal end (33) of the valve is attached to the ring (53) portion of the anchoring structure so that the ring (53) provides support to the inflow annulus (33) of the valve.
  • the Inflow ring (53) comprises an undulating or zigzag pattern for tire-like traction against the vessel wall.
  • the anchoring structure portion surrounding the proximal end (33) of the valve is preferably flared in an outward direction to improve anchoring forces against the vascular wall.
  • the three posts (52) extend from the proximal end (33) to the distal end (34) of the valve and provide cantilevered support to the tab regions (35) of the valve at the distal end (34).
  • the three posts (52) are designed to be sufficiently flexible so that they may deflect inwardly in a controlled motion at back flow pressures to optimize the fatigue life of the anchoring structure.
  • the posts (52) comprise a distal end (54) for the attachment of the valve commissural tabs (35). Below the distal end (54), the posts (52) comprise a diamond-shaped element (55) for enhanced structural stability and valve support.
  • the design according to the present embodiment creates open space between the proximal (33) and distal ends of the valve (34).
  • the support posts (52) are configured to spatially coincide with the commissural posts of the valve sinuses for ease of positioning and anatomical optimization.
  • the anchoring structure embodiment illustrated in Figure 14 comprises a valve supported by a multi-operational anchoring structure (56).
  • the multi-operational anchoring structure (56) comprises a proximal end (57), a distal end (58), posts (59) extending from the proximal end (57) to the distal end (58), and a tab attachment window (60) attached to each post (59) at the distal end (58).
  • the tab attachment windows (60) in the present embodiment have a triangular geometry that is designed to create an optimal interference fit between the anchoring structure and the commissural tabs.
  • the post (59) and tab attachment window (60) construction of the present embodiment allows inward deflection of the post at back flow pressure, thus providing cantilevered support to the valve and greater dynamic compliance with the sinus region.
  • Both the proximal (57) and distal (58) ends of the anchoring structure are flared out to better secure the valve in the valvular sinus region.
  • the proximal end or inflow rim (57) of the anchoring structure also preferably possesses barbs or hooks (61) at the proximal end (62) of the post (59) for better attachment to the vascular wall and/or the valve's inflow annulus.
  • the flared inflow rim (57) is depicted as featuring two undulating rings that are substantially parallel to one another, while the flared outflow rim features three undulating rings.
  • FIG. 15-21 Yet another preferred embodiment of a valve anchoring device according to the present invention is illustrated in Figures 15-21 .
  • an elliptical segment (70) anchoring structure is used to support the valve (32) as shown in Figure 15 A .
  • the elliptical segment anchoring structure (70) comprises a plurality of elliptical segments (71) that are joined together, either integrally, mechanically, or by adhesive means.
  • Each elliptical segment (71) is flared outward at the proximal (72) and distal ends (73) of the anchoring structure and curved inward at the junctures (74) with the other segments (71) assuming the shape of a potato chip.
  • the elliptical segments (71) When joined together side by side, the elliptical segments (71) form a tubular structure that is flared outward at both the inflow (72) and outflow (73) ends.
  • the junctures (74) of the elliptical segments (71) are located at the center of a substantially straight area of the elliptical segments (71) that defines the longitudinal support post elements (75) of the elliptical segment anchoring structure (70) and also provides a gap location (75) near which the valve tabs (35) can be secured.
  • the tab regions (35) extending from the seams of the valve can be attached to the anchoring structure using any suitable means, including, sewing, stapling, wedging or adhesive means.
  • the tab regions (35) are preferably attached to the gaps (75) formed above the junctures (74) between the elliptical segments (71).
  • the inflow (72) and outflow (73) rims of the anchoring structure are formed by the corresponding regions of the elliptical segments (71) that reside below and above the junctures (74).
  • the inflow annulus of the valve can be secured at the inflow rim (72) via stitching to the inflow annulus fabric which also serves as a sealing gasket.
  • FIG 16 A shows how both the valve (32) and anchoring structure (70) of the present embodiment can be compressed radially to facilitate implantation.
  • the concave configurations of the elliptical segments (71) effectively form a radial spring that is capable of being radially collapsed under pressure for deployment and then expanded when positioned at the implant site.
  • One advantageous feature of the instant design is that the region of juncture (74) between the elliptical segments (71) does not become extended upon compression of the anchoring structure.
  • the valve (32) and anchoring structure (70) of the present embodiment can also be compression fit within a valve sinus cavity to exert radial force against the sinus walls.
  • the anchoring structure (70) is preferably dimensioned to be lodged substantially within a valve sinus, with the regions of juncture (74) between the elliptical segments (71) being configured to reside at the location of the native commissural posts.
  • the elliptical segment anchoring structure (70) is designed to expand at the proximal end (72) during peak flow and at the distal end (73) during peak backflow pressure, thereby maintaining pressure against the vascular wall.
  • the valve and anchoring structure (70) of the present embodiment will remain secure in the valve sinus without sutures.
  • a metal wire frame made from a metal that exhibits a high modulus of elasticity and that is biocompatible is preferred, such as Nitinol, as such materials exhibiting superior compressibility allow the anchoring structure to be self-expandable.
  • FIG. 18 A and B A further preferred embodiment of a valve anchoring structure according to the present invention is illustrated in Figures 18 A and B .
  • an elliptical segment anchoring structure (70) is presented in which the elliptical segments (71) are joined together by a specialized double crimp (78).
  • Figure 18 B shows that the valve tabs (35) can be secured near the double crimp (78) that joins the elliptical segments (71).
  • the tab regions (35) are preferably attached to the gaps (75) between the elliptical segments (71).
  • the inflow annulus of the valve (33) can be secured at the inflow rim (72) via stitching to the inflow annulus fabric which also serves as a sealing gasket.
  • Figures 19 A and B illustrate the double crimp (78) used to join the elliptical segments (71).
  • the double crimp (78) comprises two hollow tubes (79), one for each elliptical segment (71) to be inserted.
  • the hollow tubes (79) of the double crimp (78) are designed to allow for better motion of the individual elliptical segments (71) and to minimize material stresses during expansion and compression of the anchoring structure.
  • the double crimp (78) further comprises a central portion (80) joining the two hollow tubes (79).
  • This central portion (80) comprises one or more holes (81) to facilitate the attachment of the valve commissural tabs to the anchoring structure and to reduce the mass of the double crimp (78).
  • the double crimp (78) also serves as an attachment site for the valve and further acts as a stop against backflow pressure on the valve leaflets.
  • Figure 20 A shows the insertion of the elliptical segments (71) of the preferred anchoring structure embodiment (70) into the double crimp (78).
  • the present embodiment is dimensioned to be lodged substantially within the valve sinuses, with the joined regions (74) of the elliptical segments in Figure 20 B configured to align with the commissural posts of the sinus and the flared inflow (72) and outflow ends (73) of the anchoring structure configured to rest against the sinus cavities.
  • Figures 21 A throughG show how the elliptical segment anchoring structure (70) may additionally be covered with cloth (82), particularly at the inflow end (72) to provide traction and a gasket-like seal.
  • this preferred embodiment of the present invention is dimensioned to follow the sinus architecture and to lodge into the sinus cavities and against the Inflow and outflow annuli of the sinuses for optimal securing and positioning of the replacement valve.
  • FIGS 22 A and B illustrate a further preferred embodiment the present invention.
  • This figure shows an elliptical segment anchoring structure (90) made from one piece of tubing.
  • the support posts (91) that form the slots (92) for the valve tabs include a series of small holes (93) on either side of the slot (92) to facilitate suture or mechanical attachment of the commissural tabs of the valve.
  • this anchoring structure (90) is dimensioned to fit substantially within the valve sinuses with the support posts (91) being configured to reside in the commissural posts between the individual sinus cavities.
  • the present embodiment also exerts axial force particularly at the flared inflow (94) and outflow rims (95) against the sinus walls to anchor the valve.
  • FIG. 23 A Yet another embodiment of a valve and anchoring structure according to the present invention is illustrated in Figures 23 A through D .
  • a claw anchoring structure (100) is shown in Figure 23 A .
  • This embodiment corresponds to an elliptical segment embodiment wherein the upper portions of each elliptical segment have been removed.
  • the ends of the junctures (101) of the remaining elliptical segments are shaped into prongs or claws (102).
  • the claw anchoring structure (100) comprises a flexible spring frame having a plurality of barbs (102), located distally just beyond where the valve leaflet tab regions meet the anchoring structure.
  • the claw anchoring structure (100) preferably comprises at least one barb (102) for each valve leaflet tab included in the valve.
  • the barbs (102) are designed to anchor the valve (32) and anchoring structure (100) to the vascular wall.
  • an anchoring structure that lacks vertical support posts.
  • the representative anchoring structure configuration comprises an inflow ring (110) that is adapted to being secured to the inflow annulus of the valve (33) via stitching to the reinforced fabric sewing ring in a manner similar to the prior representative implementations.
  • the undulating or sinusoidal pattern of the ring (110) facilitates radial collapse and expansion and exerts radial force against the vessel wall.
  • the anchoring structure does not support the outflow annulus (34) of the valve. Rather, the valve's commissural tabs (35) are attached to the sinus walls via mechanical means, such as sutures, staples, or wire.
  • the present embodiment comprises a dual-ring anchoring structure (120).
  • the dual ring (120) of the present embodiment may, as in the previous embodiment, be secured to the inflow annulus of the valve via stitching to the reinforced fabric sewing ring.
  • the undulating or sinusoidal pattern of the individual rings (121) is configured such that the peaks (122) of one ring (121) coincide with the valleys (123) of the other ring and vice versa, thereby forming a sine-cosine pattern. This pattern facilitates radial collapse and expansion and exerts radial force against the vessel wall.
  • the dual ring anchoring structure (120) does not support the outflow annulus of the valve. Rather, the valve's commissural tabs are attached to the native sinus walls via mechanical means, such as sutures, staples, or wire, or additionally by the adhesive means disclosed herein.
  • FIG 25 B shows another dual ring embodiment of the present invention.
  • This anchoring structure is comprised of an upper (distal) dual ring (130) and a lower (proximal) dual ring (131).
  • the lower dual ring (131) is connected to the proximal end of the valve at the inflow annulus while the upper dual ring (130) is connected to the distal end of the valve at the outflow annulus.
  • the valve may be connected to the rings (130, 131) via sutures, clips or any other suitable means for attachment.
  • the valve and the attached proximal (131) and distal (130) rings can be collapsed and inserted via a catheter.
  • each dual ring (130, 131) comprises a wire frame with a circular cross-section and a sinusoidal pattern.
  • the sinusoidal pattern may be of a sine-cosine shape with a varied frequency and amplitude.
  • One or more longitudinal rods (132) may be used to connect the two dual rings (130, 131) and maintain longitudinal separation and radial orientation. The rods (132) may be removable so that once the valve is implanted in the vascular passageway they can be removed.
  • an upper single ring (140) with an undulating or zigzag pattern provides support to the tab regions (35) of the valve (32) at the distal end (34) of the valve whereas a lower single ring (141) configured in an undulating or sinusoidal pattern provides support to the inflow annulus (33) at the proximal end of the valve (32).
  • the inflow ring (141) is stitched to the sewing fabric wrapped around the circumference of the inflow annulus of the valve, as described previously.
  • the outflow ring (140) of the anchoring structure generally resides above the leaflets (36) to avoid leaflet contact.
  • the inflow or outflow rings may comprise attachment barbs (142).
  • the structural dissociation between the rings (140, 141) provides improved dynamic compliance while retaining the benefits of a two ring design.
  • FIG. 27A through C Yet another embodiment of a valve and anchoring structure according to the present invention is illustrated in Figures 27 A through C .
  • the valve (32) is supported by a tubular anchoring structure (150).
  • the tubular anchoring structure (150) is preferably made of metal or plastic.
  • the tubular anchoring structure (150) is also preferably designed to be expandable.
  • the anchoring structure may be designed to be self-expandable, balloon-expandable, or mechanically-expandable.
  • the tab regions (35) of the valve (32) are preferably attached to the distal end (151) of the tubular anchoring structure (150) using staples, sutures, wire fasteners, or any other suitable means.
  • the inflow rim (152) of the tubular anchoring structure may comprise a plurality of suture bores (153) to facilitate attachment of the valve (32).
  • the tubular anchoring structure (150) also comprises vertical support posts (154) with axial slots (155) for the insertion of the valve tabs (35).
  • the vertical support posts (154) extend to the distal end (151) of the tubular anchoring structure (150).
  • the means of attachment or an alternative means, is used to also attach the tab regions (35) of the valve (32) to the vascular wall thereby securing the valve (32) and tubular anchoring structure (150) in the valve sinuses.
  • Such fastening means can also be optionally used at the inflow annulus to provide additional anchoring.
  • FIG. 28 Another embodiment of a valve and anchoring structure according to the present invention is illustrated in Figure 28 .
  • a dual-ring anchoring structure (160) is shown, as seen in Figures 28 C and D , with an inflow ring (161) and an outflow ring (162) connected by a vertical element (163) comprised of two posts (164).
  • the anchoring structure (160) is designed to be circumferentially collapsible as can be seen in Figures 28 A and B .
  • the anchoring structure (160) is collapsed by sliding the two posts (164) that are adjacent to each other in the expanded state ( Figure 28 D) past each other to decrease the circumference of the upper outflow (162) and lower inflow (161) rings ( Figure 28 C) .
  • the anchoring structure (160) prior to implantation the anchoring structure (160) is collapsed and, once the valve is properly positioned in the valve sinuses, the anchoring structure freely self-expands to its original dimensions.
  • the self-expanding behavior of the present embodiment is due to Nitinol's relatively high modulus of elasticity, which imparts superior spring-like properties to the anchoring structure.
  • the anchoring structure is constructed of a non-self expanding material, it may be mechanically collapsed and expanded using the devices disclosed herein.
  • FIGS 29 A and B Another embodiment of a valve and anchoring structure according to the present invention is illustrated in Figures 29 A and B .
  • a dual-ring anchoring structure (170) is shown, with an inflow ring (171) and an outflow ring (172) connected by a vertical element (173) comprised of two posts (174).
  • the inflow rim may further comprise tissue mounting posts (175).
  • the anchoring structure (170) is designed to be circumferentially collapsible.
  • Figure 29 A shows how the posts (174) are separated in the expanded state and
  • Figure 29 B shows how the posts (174) form a single vertical element (173) in the collapsed state.
  • the anchoring structure prior to implantation the anchoring structure is collapsed and upon the positioning of the valve assembly in the valve sinuses, the anchoring structure (170) freely self-expands to its original dimensions.
  • the self-expanding behavior of the present embodiment is a function of Nitinol's high modulus of elasticity.
  • the anchoring structure is constructed of a non-self expanding material, it may be mechanically collapsed and expanded using the devices disclosed herein.
  • FIG. 30 A and B A further embodiment of a valve and anchoring structure according to the present invention is illustrated in Figures 30 A and B .
  • the present embodiment comprises a spring-aided anchoring structure (180).
  • the spring aided anchoring structure (180) preferably comprises three members (181) that are radially collapsible for implantation into the valve sinuses.
  • the members (181) comprise peaks (182) that serve as valve attachment points and valleys (183) that serve to lodge the anchoring structure at the valve sinus inflow annulus.
  • the anchoring structure (180) is expanded to its original dimensions by coil springs (184) that provide an outward radial force on each member.
  • the spring aided anchoring structure (180) comprises at least one anchoring section (185) for selectively securing the anchoring structure (180) in the valve sinus at the inflow annulus.
  • the present embodiment illustrates three members (181) and three coil springs (184), it should be appreciated that two or more members (181) with a corresponding number of coil springs (184) may be used.
  • the anchoring structures of the present invention may be constructed from superelastic memory metal alloys, such as Nitinol, described in U.S. Patent No. 6,451,025 , incorporated herein by reference.
  • Nitinol belongs to a family of intermetallic materials which contain a nearly equal mixture of nickel and titanium. Other elements can be added to adjust or modify the material properties.
  • Nitinol exhibits both shape memory and superelastic properties.
  • the shape memory effect of Nitinol allows for the restoration of the original shape of a plastically deformed structure by heating it. This is a result of the crystalline phase change known as thermoelastic martensitic transformation.
  • Nitinol is martensitic, i.e.
  • the valve assembly Prior to implantation, the valve assembly is chilled in sterile ice water. Upon cooling, the Nitinol anchoring structure enters its martensite phase. Once in this phase, the structure is malleable and can maintain a plastically deformed crushed configuration. When the crushed anchoring structure comprising the valve is delivered into the valve sinus, the increase in temperature results in a phase change from martensite to austenite. Through the phase change, the anchoring structure returns to its memorized shape, and thus expands back to its original size.
  • the anchoring structures can also be designed to use the superelasticity properties of Nitinol. With the superelastic design, the chilling procedure would not be necessary. The anchoring structure would be crushed at room temperature. The phase change to martensite would be accomplished by means of the stress generated during the crushing process. The anchoring structure would be held in the crushed configuration using force. Force is removed once the anchoring structure is delivered to the valve sinus, resulting in a phase transformation of the Nitinol from martensite to austenite. Through the phase change, the anchoring structure returns to its memorized shape and stresses and strains generated during the crushing process are removed.
  • the anchoring structures of the present invention may be composed of a non-self expanding suitable material, such as biocompatible metals, including titanium, and plastics. Whether the valve assembly is designed to be self-expandable or non-self expandable, it may be compressed (and expanded, if non-self expandable) for implantation using the expansion and contraction devices disclosed herein.
  • FIG. 31-33 A preferred embodiment of an expansion and contraction device for implanting the valve assemblies of the present invention is illustrated in Figures 31-33 .
  • the device of the present embodiment comprises a group of bendable hollow tubes or wires (200), a grip handle (201), and a circular element (202) that holds the wires (200) together at their proximal ends (203).
  • Each wire (200) comprises a proximal end (203), a distal end (204) and a hollow shaft (205) running from the proximal end (203) to the distal end (204).
  • the wires (200) are attached to the grip handle (201) at their proximal ends (203) via the circular element (202) such that the wires form a circular pattern.
  • the expansion and contraction device further comprises a cylinder (206) having a proximal end (207) and a distal end (208).
  • the cylinder (206) has holes (209) drilled along its distal perimeter (208).
  • the holes (209) in the cylinder (206) are preferably drilled at an outward angle so that by forcing the wires (200) through the angled holes (209), the distal ends (204) of the wires (200) are driven radially outward.
  • the angle of the cylinder holes (209) controls the relationship between the longitudinal movement of the wires (200) and their radial dilation.
  • a representative anchoring structure (210) of the present invention is attached to the distal ends (204) of the hollow wires (200).
  • the cylinder (206) having a proximal end (207) and a distal end (208) has holes (209) drilled along its distal perimeter (208).
  • the holes (209) in the cylinder (206) are drilled at an outward angle so that by forcing the wires (200) through the angled holes (209), the distal ends (204) of the wires (200) are driven radially outward.
  • the wires (200) when the wires (200) are pushed further through the outwardly angled cylinder holes (209), they are forced to spread radially, thereby expanding the anchoring structure (210) that is positioned over the wires (200) at their distal ends (204).
  • a long suture is routed from the proximal end to the distal end of the wire down its hollow shaft, looped around a segment of the anchoring structure at the distal end of the wire and then routed back to the proximal end of the wire, where it is secured. Attached to the distal ends (204) of the hollow wires, the anchoring structure (210) contracts and expands radially in response to the longitudinal motion of the wires (200).
  • the grip handle (201) proximally contracts the anchoring structure (210) into a collapsed state for implantation whereas pushing the grip handle (201) distally expands the anchoring structure (210).
  • the anchoring structure (210) is positioned in a desirable location in the vessel and expanded to the desired dimensions, the sutures are severed and removed from the proximal end (203) of the wires (200) in order to disconnect the anchoring structure (210) from the device.
  • the device of the present embodiment is removed, thereby leaving the valve assembly securely situated in the valve sinus.
  • the device of the present embodiment comprises a tube (220), multiple wall panels (221), springs (222) corresponding to the multiple wall panels (221), a spindle (223) and a plurality of connecting wires (224).
  • the tube (220) comprises a hollow shaft (225) having a radial center (226), a proximal end (227), a distal end (228) as shown in Figure 35 , an interior wall (229) and an exterior wall (230), wherein a hole (231) corresponding to each wall panel (221) extends through the interior (229) and exterior wall (230) of the tube (220).
  • the perimeter of the exterior wall (230) is surrounded by adjacent wall panels (221), only buffered by the springs (222) corresponding to the wall panels (221).
  • the spindle (223) is attached to the interior wall (229) of the tube (220), preferably facing the tube's (220) radial center (226).
  • a connecting wire (224) is attached to each wall panel (221) and routed through the spring (222) and the corresponding hole (231) in the tube wall (229, 230) to meet the other connecting wires (224), preferably at the radial center (226) of the tube (220).
  • the length of the uncompressed spring (222) determines the diameter to which the anchoring structure can be expanded.
  • the anchoring structure can optionally be secured to the wall panels (221), by staples, sutures, wire fasteners, or any other suitable means, so that the valve assembly may be selectively expanded and collapsed by preferably varying the tension on the connecting wires.
  • the anchoring structure (240) is composed of a shape memory metal or the like having a relatively high modulus of elasticity, and possessing an outward spring-like force when in a compressed state. Therefore, spring loaded wall panels are not necessary in the present embodiment. Instead, the wires (241) pass through sutures (242) that are threaded through holes (243) in the tube (244) wall and wrap around portions of the anchoring structure. Thus, the wires (241) keep the anchoring structure (240) compressed by pulling the sutures (242) around the anchoring structure (240) against the tube (244).
  • the tube structure can be omitted with only the wires (241) and sutures (242) keeping the anchoring structure (240) in a compressed state. This would ensure that the valve within the anchoring structure is not contacted by any mechanical elements, such as a tube (244).
  • the tube could be made from a cloth- or tissue-like material.
  • each wall panel (250) is connected to a pin (251) which runs through the corresponding hole (252) in the tube (253) wall.
  • the pin (251), protruding radially inward from the tube's interior, is preferably spring-loaded (254) toward the radial center of the tube (253).
  • the wall panels (250) rest against the exterior wall of the tube (253) and the collapsed anchoring structure rests against the wall panels (250).
  • the present embodiment comprises a longitudinal shaft (255) running through the radial center of the tube.
  • the shaft is comprised of a proximal end (256) and a distal end (257).
  • the distal end (257) is connected to a central plate (258) having spiral shaped edges (259) as shown in Figures 37 B and C .
  • the central plate (258) is located in the tube (253), parallel to the tube's cross-section and is aligned with the spring-loaded (254) pins (251).
  • the plate's spiral-shaped edges (259) preferably cause the distance from the plate's perimeter to the tube's radial center to vary along the plate's (258) perimeter.
  • Figures 38 A and B show how rotation of the shaft (255) pushes the wall panels (250) radially out, thereby expanding the anchoring structure (260).
  • the anchoring structure (260) is sutured to the wall panels (250) to allow expansion and contraction of the anchoring structure by alternating rotation of the shaft.
  • the sutures are preferably removable from the shaft's (255) proximal end to free the valve assembly from the device following implantation in the valve sinus.
  • an expansion and contraction device similar to the previous embodiment is presented.
  • the present preferred embodiment utilizes a circular disk (270) with pre-cut spiral-shaped grooves (271) corresponding to the spring-loaded pins (272).
  • the grooves (271) provide a track of varying depth for the pins (272) such that the pins (272) are forced radially outward upon rotation of the disk (270), thereby expanding the anchoring structure.
  • the present invention provides the use of biocompatible adhesives.
  • a number of adhesives may be used to seal the valve assembly to the surrounding tissue in the valve sinus. The following are examples of available adhesives and methods of use:
  • U.S. Pat. No. 5,549,904 discloses a formulated biological adhesive composition
  • a formulated biological adhesive composition comprising tissue transglutaminase and a pharmaceutically acceptable carrier, the tissue transglutaminase in an effective amount to promote adhesion upon treatment of tissue in the presence of a divalent metal ion, such as calcium or strontium.
  • a divalent metal ion such as calcium or strontium.
  • the two components are mixed to activate the sealable fixation means for securely fixing the valve assembly to tissue at a desired valve location.
  • U.S. Pat. No. 5,407,671 discloses a one-component tissue adhesive containing, in aqueous solution, fibrinogen, F XIII, a thrombin inhibitor, prothrombin factors, calcium ions and, where appropriate, a plasmin inhibitor.
  • This adhesive can be reconstituted from a freeze-dried form with water. It can contain all active substances in pasteurized form and is then free of the risk of transmission of hepatitis and HTLV III.
  • the one-component tissue adhesive is reconstituted from a freeze-dried form with water to activate the sealable fixation means for securely fixing the valve assembly to tissue at a desired valve location.
  • U.S. Pat. No. 5,739,288 discloses a method for utilizing a fibrin sealant which comprises: (a) contacting a desired site with a composition comprising fibrin monomer or noncrosslinked fibrin; and (b) converting the fibrin monomer or noncrosslinked fibrin to a fibrin polymer concurrently with the contacting step, thereby forming a fibrin clot.
  • the fibrin monomer or noncrosslinked fibrin is converted to activate the sealable fixation means for securely fixing the valve assembly to tissue at a desired valve location.
  • U.S. Pat. No. 5,744,545 discloses a method for effecting the nonsurgical attachment of a first surface to a second surface, comprising the steps of: (a) providing collagen and a multifunctionally activated synthetic hydrophilic polymer; (b) mixing the collagen and synthetic polymer to initiate crosslinking between the collagen and the synthetic polymer; (c) applying the mixture of collagen and synthetic polymer to a first surface before substantial crosslinking has occurred between the collagen and the synthetic polymer; and (d) contacting the first surface with the second surface to effect adhesion between the two surfaces.
  • Each surface can be a native tissue or implant surface.
  • collagen and a multifunctionally activated synthetic hydrophilic polymer are mixed to activate the sealable fixation means for securely fixing the valve assembly to tissue at a desired valve location.
  • U.S. Pat. No. 6,113,948 discloses soluble microparticles comprising fibrinogen or thrombin, in free-flowing form. These microparticles can be mixed to give a dry powder, to be used as a fibrin sealant that is activated only at a tissue site upon dissolving the soluble microparticles. In operation, soluble microparticles comprising fibrinogen or thrombin are contacted with water to activate the sealable fixation means for securely fixing the valve assembly to tissue at a desired valve location.
  • thermally activatable adhesive is an adhesive which exhibits an increase in "tack" or adhesion after being warmed to a temperature at or above the activation temperature of the adhesive.
  • the activation temperature of the thermally activatable adhesive is between about 28° C and 60° C. More preferably, the activation temperature is between about 30° C and 40° C.
  • One exemplary thermally activatable adhesive is described as Example 1 in U.S. Pat. No. 5,648,167 , which is incorporated by reference herein.
  • Figure 40 shows a preferred embodiment, wherein an outer circumferential reservoir (401) is located at an outermost radius of a valve anchoring structure (400) when the anchoring structure (400) is in an expanded state, wherein the reservoir is filled with a sealable fixation means for securely fixing the valve assembly (400) at a desired location within a body cavity.
  • Figure 40 further illustrates one embodiment of the reservoir (401) comprising a sealable fixation means, wherein the sealable fixation means may comprise a one-component biological adhesive.
  • the sealable fixation means may be activated by exposing the biological adhesive to blood or heat.
  • Figure 41 illustrates another preferred embodiment wherein the sealable fixation means may comprise a two-component biological adhesive.
  • the sealable fixation means may be activated by mixing the two components.
  • the second reservoir (403) would contain the water for the activation of the microparticles.
  • the reservoirs may be arranged concentrically as shown in Figure 41 B or adjacent to each other as shown in Figure 41 A .
  • Figure 42 illustrates an exemplary reservoir (401) which may be attached to the valve anchoring structure by its Inner wall (404) by sutures, glue, staples or some other appropriate method.
  • Figure 42 further illustrates a thin spot (405) on the outer wall (406) of the reservoir (401).
  • the thin spots (405) are areas on the reservoir (401) that are adapted to rupture when placed under certain levels of pressure. The pressure is exerted on the thin spots (405) as the reservoir (401) is expanded along with the valve anchoring structure. The thin spots (405) are unable to withstand the pressure and therefore rupture releasing the contents of the reservoir (401) or reservoirs.
  • the reservoir (401) is made of an elastic material that expands along with the expansion of the valve anchoring structure.
  • Figure 43 illustrates a cross sectional view of the reservoir (401).
  • the reservoir (401) may contain a lumen (407) which extends along at least a portion of the circumference of the reservoir.
  • the reservoir (401) has one or more thin spots (405) along its outermost circumference, wherein the thin spots (405) are sized and configured to rupture when the reservoir (401) is expanded to an appropriate diameter. When the anchoring structure comprising the valve is fully expanded, the pressure exerted upon the expanded thin spots (405) causes them to rupture.
  • the reservoir (401) is made of a biodegradable material adapted for erosion or rupture to release the content of the reservoir (401) and activate the sealable fixation means in a desired timeframe after implantation.
  • a circumferentially outermost portion is pressure sensitive to rupture, wherein the contents of the reservoir (401) are released when the reservoir (401) is compressed against the sinus cavities during expansion and implantation of the valve assembly.
  • Figure 44 shows a cross-sectional view of another preferred embodiment, illustrating thin spots (405) on a reservoir having two concentric component compartments, an inner compartment (408) and an outer compartment (409).
  • Component A in an inner compartment (408) and component B in an outer compartment (409) are to be mixed to form adhesive for sealing the valve assembly against the valve sinuses.
  • the inner compartment (408) has a plurality of thin spots (405) along its outermost circumference, wherein the thin spots (405) are sized and configured to rupture when the reservoir (401) is expanded to an appropriate diameter.
  • the outer compartment (409) also has a plurality of thin spots (405) along its innermost circumference.
  • the thin spots (405) of the inner compartment (408) and the thin spots (405) of the outer compartment (409) may be located adjacent to each other.
  • the space between the adjacent pair of thin spots (405) on the inner (408) and outer (409) compartment may comprise a piercing element that is activated to rupture the thin spot or the pair of adjacent spots when the reservoir is expanded to an appropriate diameter or a predetermined diameter.
  • Other embodiments of reservoir configuration, for example, two parallel compartments circumferentially or longitudinally, and suitable activation mechanism for the sealable fixation means are also within the scope of the present invention.
  • the present invention further comprises methods and devices for the sizing of native valves that require replacement.
  • Intravascular ultrasound uses high-frequency sound waves that are sent with a device called a transducer.
  • the transducer is attached to the end of a catheter, which is threaded through a vein, artery, or other vessel lumen.
  • the sound waves bounce off of the walls of the vessel and return to the transducer as echoes.
  • the echoes can be converted into distances by computer.
  • a preferred minimally invasive valve replacement sizer is shown in Figures 45 A and B .
  • the distal end or portion refers to the area closer to the body while the proximal end or portion refers to the area closer to the user of the valve replacement sizer.
  • the device comprises a guidewire (500), an intravascular ultrasound (IVUS) catheter (501) having a transducer (502), and a balloon dilatation catheter (503) all positioned within the central lumen of a catheter.
  • the transducer (502) is positioned in the IVUS sizing window (504) of the balloon catheter.
  • the guide wire (500) advances and guides the catheter (501) to the appropriate location for valve sizing.
  • Figure 45 A shows the catheter in deflated form, whereas in Figure 45 B the balloon dilatation catheter (503) has inflated the balloon (505).
  • the catheter (510) contains multiple lumens (511) in order to house a guidewire (512), an IVUS catheter (513), and a balloon dilatation catheter (514).
  • Figure 46 illustrates a cross sectional view.
  • One of the separate lumens (511) contains the guidewire (512), another contains the IVUS catheter (513), and another contains the balloon dilatation catheter (514).
  • the balloon dilatation catheter (514) has a balloon (515) attached circumferentially surrounding the balloon dilatation catheter (514) as well as a portion of the catheter (510).
  • Figure 47 shows a balloon dilatation catheter (516) comprising a balloon (517) that circumferentially surrounds a portion of the catheter (518) proximal to its distal portion (519). More specifically, the balloon (517) comprises an outer wall (520) that circumferentially surrounds a portion of the catheter (518) near its distal portion (519). The balloon (517) also has a distal end (521) and a proximal end (522). In a preferred embodiment, within the area encompassed by the balloon, a transducer (523) is located on the IVUS catheter (524).
  • a sizing window (525) is placed on the IVUS catheter (524) to enable signals to be transmitted and received by the transducer (523) without interference.
  • the sizing window (525) is simply an empty space.
  • the sizing window (525) could be made from any substance which does not interfere with the signals emitted and received by the transducer (523).
  • the balloon (517) is round but other shapes are possible and contemplated for use with the valve sizing apparatus.
  • Figure 48 shows a cross section of an inflated balloon (530) with curves forming leaflets (531) to enable fluid (532) to pass through the vessel while the balloon (530) is in its inflated state and the outer edges (533) of the leaflets (531) are in contact with the vessel wall (534) to measure the diameter.
  • the balloon may further be made from compliant or non-compliant material.
  • Figure 49 shows a preferred embodiment wherein the balloon (540) is inflated with saline (541).
  • the saline is pumped into the balloon (540) through the balloon dilatation catheter.
  • the balloon (540) may be inflated with a gas or any other suitable substance.
  • the balloon (540) is inflated to a chosen pressure by the person using the valve replacement sizer.
  • the outermost portion of the outer wall (542) will be in contact with the vessel wall (543) or other lumen at the location where the replacement valve is to be placed.
  • the farthest radial points of the balloon's outer wall (542) will be equidistant to the center of the catheter (544).
  • the transducer (545) may or may not be at the centermost point of the inflated balloon (540). Any deviation from the centermost point by the transducer (545) may be accounted for when calculating the diameter of the vessel lumen. However, the signal emitted by the transducer (545) preferably intersects the balloon (540) at its greatest radius.
  • Figure 50 shows a preferred embodiment, wherein a transducer (550) emits an ultrasonic signal (556) in a perpendicular direction to the IVUS catheter (551). The signal is then reflected off the outer wall (552) of the balloon (540) and received by the transducer (550). The transducer (550) then transmits the data to the auxiliary processor (553) to determine the radius and diameter of the vessel lumen. Alternatively, an infrared light may be emitted and received by the transducer (550) to determine the radius and diameter of the vessel lumen. The diameter is calculated by knowing the speed of the signal and the time it takes for the signal to be reflected off the balloon wall (552) back to the transducer (550). The known speed is multiplied by the time to determine the radius of the balloon (540). The radius may be adjusted if the transducer (550) was not located at the centermost point of the catheter.
  • the present invention further provides devices and methods to remove the native diseased valves prior to implantation of the replacement valve assembly.
  • the valve removing means is provided by the replacement valve assembly.
  • the valve removing means is provided by a valve sizing device of the present invention.
  • the present invention further provides valve assemblies comprising native valve removing capabilities.
  • a valve anchoring structure having cutting means located at the annulus base for cutting a native valve is provided. Accordingly, when passing the valve assembly comprising the valve and anchoring structure through the vessel with the anchoring structure in a collapsed state, the cutting means can be advanced against the native valve with the anchoring structure in a partially expanded state. In this manner, the anchoring structure comprising the cutting means cuts at least a portion of the native valve by deploying the cutting means, before the valve assembly is secured to the desired valve location with the anchoring structure in the expanded state.
  • the native valve removing means on the anchoring structure is selected from a group consisting of: a plurality of sharp edge elements, each sharp edge element having a sharp end enabling the element to cut through at least a portion of the native valve; a plurality of electrode elements, wherein radiofrequency energy is delivered to each electrode element enabling the electrode element to cut through at least a portion of the native valve, and a plurality of ultrasound transducer elements, wherein ultrasound energy is delivered to each transducer element enabling the transducer element to cut through at least a portion of the native valve.
  • valve anchoring structure is made from a radially collapsible and re-expandable cylindrical support means for folding and expanding together with the collapsible replacement valve for implantation in the body by means of catheterization or other minimally invasive procedure.
  • catheter balloon systems are well known to those of skill in the art, for example, U.S. Pat. No. 6,605,056 issued on August 23, 2003 .
  • the anchoring structure (600) comprises at least one ultrasound transducer (601) at the distal end portion of the lower ring (602), wherein each ultrasound transducer is sized and configured with ultrasound energy as cutting means for cutting a native valve.
  • Ultrasound energy is delivered through conductor means (603) to each transducer element (601) enabling the transducer element (601) to cut through at least a portion of the native valve.
  • the conductor (603) passes through a delivery means and is connected to an external ultrasound energy generator.
  • the ablative ultrasound delivery means and methods are well known to one skilled in the art, for example, U.S. Pat. No. 6,241,692 issued on June 5, 2001 .
  • Figure 52 shows another preferred embodiment of a native valve removal system comprising a valve assembly having radiofrequency cutting means.
  • the anchoring structure comprises at least one radiofrequency electrode (610) at the distal end portion of the lower ring (602), wherein each radiofrequency electrode (610) is sized and configured with radiofrequency energy as cutting means for cutting a native valve.
  • Radiofrequency energy is delivered through conductor means (611) to each electrode element (610) enabling the electrode element to cut through at least a portion of the native valve.
  • the conductor (611) passes through delivery means and is connected to an external radiofrequency energy generator.
  • the ablative radiofrequency delivery means and methods are well known to one skilled in the art, for example, U.S. Pat. No. 6,033,402 issued on March 7, 2000 .
  • Figure 53 shows another embodiment of an anchoring structure having sharp edge cutting means (620).
  • the anchoring structure comprises a set of sharp edge cutting elements (621) at the distal end portion of the cutting means (620) of the lower ring (602) of the anchoring structure, wherein each cutting element (621) has a cutting tip (622), and wherein each cutting element (621) of the cutting means is sized and configured, optionally with radiofrequency energy, as cutting means for cutting a native valve.
  • sharp edge cutting means on the delivery apparatus is rotatable, enabling the cutting element (621) to cut through at least a portion of the native valve.
  • Sharp edge cutting means with optionally ablative radiofrequency delivery means and methods, are well known to one skilled in the art, for example, U.S. Pat. No. 5,980,515 issued on November 9, 1999 .
  • Figure 54 shows a partially inflated balloon catheter.
  • a balloon catheter (630) is introduced in the vessel.
  • the balloon means (632) of the balloon catheter (630) is led out of the protection cap (633) at the catheter tip (634) and is partly inflated through a fluid channel (635), which is led to the surface of the patient.
  • the balloon (632) is partially expanded and the sharp end (636) of the cutting means of the valve anchoring structure (637) is advanced to cut and remove at least a portion of the native valve.
  • the valve anchoring structure (637) comprises an ultrasound or radiofrequency cutting means (638).
  • the support structure is expanded at about 30 to 95% of full expansion for cutting the native valve. More preferably, the support structure is expanded at about 50 to 90% of the full expansion.
  • the balloon catheter (630) comprises a central channel (639) with respect to a central axial line (640) to receive a guide wire (641) which is used in a way known for viewing the introduction of the catheter through fluoroscopy.
  • Some aspects of the present invention provide a method of endovascularly implanting a valve through a vessel, comprising the steps of providing a collapsibly expandable valve assembly that comprises an anchoring structure according to the present invention with an annulus base and a collapsible valve connected to the anchoring structure, the collapsible valve being configured to permit blood flow in a direction and prevent blood flow in an opposite direction, the anchoring structure having cutting means located at the annulus base for cutting a native valve, passing the valve assembly through the vessel with the anchoring structure in a collapsed state, advancing the cutting means against the native valve with the anchoring structure in a partially expanded state, cutting at least a portion of the native valve by deploying the cutting means, and securing the valve assembly to the desired valve location with the anchoring structure in the expanded shape.
  • a method of implanting a valve assembly is given below: a valve assembly made of an anchoring structure of the present invention and a collapsible valve, as described above, is placed on a deflated balloon means and is compressed thereon, either manually or by use of the expansion/compression devices of the instant invention; the balloon means and the valve assembly are drawn into an insertion cover; a guide wire is inserted into a vessel through the central opening of the balloon catheter under continuous fluoroscopy; the insertion cover conveys the guide wire to a point in the channel in the immediate vicinity of the desired position of the valve assembly; the balloon means is pushed out of the protection cap and the valve assembly is positioned in the desired position if necessary by use of further imaging means to ensure accurate positioning; the balloon means is inflated partially; the valve assembly is advanced with its cutting means cutting at least a portion of the native valve; the balloon means is further inflated to position the valve at a desired site, preferably against the truncated valvular annulus; the balloon means is
  • the present invention also provides for devices and methods to prevent the release of debris during removal of the native diseased valves from traveling to distant sites where such debris may cause undesirable physiological effects.
  • the present invention provides for specialized filters that capture material and debris generated during valve replacement procedures.
  • the distal protection devices of the present invention are also effective in trapping material that may be released during other percutaneous interventional procedures, such as balloon angioplasty or stenting procedures by providing a temporary valve and filter in the same device.
  • the present invention provides for a temporary valve (700), which may be deployed at a desired location in a collapsed state and then expanded and secured to the walls of the passageway.
  • the temporary valve (700) comprises two concentric one-way valves, an outer valve (701) and an inner valve (702) disposed within the outer valve (701), that open in opposite directions as shown in Figure 55 B .
  • the outer valve (701) opens in response to positive fluid flow pressure, thereby regulating blood flow In substantially one direction.
  • the inner valve (702) opens in the opposite direction of the outer valve (701) to facilitate the insertion of catheter based equipment (703) as shown in Figure 55 C and functions as a seal through which such equipment may be passed.
  • the pressure required to open the individual valves may be manipulated to facilitate positive fluid flow, while precluding or minimizing retrograde flow that might otherwise occur as a result of back flow pressure.
  • the inner valve (702) be configured or constructed to open with relatively more pressure than that required to open the outer valve.
  • the outer (701) and inner valves (702) of the temporary valve (700) may be coupled together by radial support members.
  • the radial support members couple the inner surface of the outer valve to the outer surface of the inner valve.
  • the length of the radial support means depends upon the dimension of the blood vessel or body cavity within which the temporary valve is to be deployed.
  • the temporary valve may be constructed from material that is capable of self-expanding the temporary valve, once it is deployed from the collapsed state at the desired location. Once expanded, catheter based equipment required for the particular surgical procedure may be passed through and movably operated in relation to the temporary valve.
  • the temporary valve may be combined with a filter that extends distally from the temporary valve to capture debris material.
  • the temporary valve-filter device is preferably configured such that the open proximal end is secured to the temporary valve and the closed distal end comprises an opening or a third valve to facilitate the passage of the catheter equipment through the distal end of the bag and out of the temporary valve. Additional valves may also be positioned in the filter to coincide with one or more branching arteries.
  • the temporary valve-filter device may include one or more traps within the filter bag to trap debris material within the bag to reduce the likelihood of debris material leaving the filter when the catheter equipment is being passed through the filter bag.
  • the filter traps may be comprised of one or more valves disposed within the filter bag that are configured to open with retrograde pressure.
  • the traps may be comprised of flaps that extend inwardly from the perimeter of the bag to create a cupping effect that traps particulate matter and directs it outwardly toward the perimeter of the filter bag.
  • the filter traps may be constructed of material that is capable of facilitating and filtering antegrade fluid flow, while retaining the debris material within the filter bag.
  • the valve-filter assembly previously described may also incorporate multiple valves. In this arrangement, debris may be better and better entrapped, and thus reduces the chance of debris coming out of the valve-filter assembly.
  • the present invention is particularly useful while performing an interventional procedure in vital arteries, such as the carotid arteries and the aorta, in which critical downstream blood vessels can become blocked with debris material.
  • the valve-filter assembly may also include a cannulation system at the downstream end of the filter to remove particles and debris.
  • the valve-filter assembly may also include a grinder for cutting up or reducing the size of the debris. This debris, in turn, may be removed by a cannulation system or be allowed to remain in the filter.
  • valve-filter assembly is well-suited for use in minimally invasive surgery where the valve-filter may be placed in the aorta between the aortic valve and the innominate branch or the braciocephalic branch.
  • the valve-filter may be put in place before the start of surgery and function as a valve.
  • the valve-filter may further collect debris and particles during removal and clean up of the old valve.
  • the valve-filter may also stay in place while the new valve is put in place and until the end of the procedure to function as protection and as a valve.
  • a vascular filter system is well known to one skilled in the art, for example, U.S. pat. No. 6,485,501 issued on November 26, 2002 .
  • the invention may be part of a catheter.
  • the invention may also be assembled onto a separate catheter.
  • the valve-filter may also be part of a non-catheter device, placed directly into a blood vessel or other lumen.
  • the valve-filter may be introduced into the body by the ways described in the following non-inclusive list: femoral artery, femoral vein, carotid artery, jugular vein, mouth, nose, urethra, vagina, brachial artery, subclavian vein, open sternotomies, partial sternotomies, and other places in the arterial and venous system.
  • the filter mesh of the valve-filter may be of any size and shape required to trap all of the material while still providing sufficient surface area for providing satisfactory flows during the use of the filter.
  • the filter may be a sheet or bag of different mesh sizes.
  • the mesh size is optimized taking the following factors into consideration: flow conditions, application site, size of filter bag, rate of clotting, etc.
  • Radiopaque markers and/or sonoreflective markers may be located on the catheter and/or the valve-filter assembly.
  • An embodiment of the valve-filter catheter is described having an aortic transillumination system for locating and monitoring the position and deployment state of the catheter and the valve-filter assembly without fluoroscopy.
  • visualization techniques including transcranial Doppler ultrasonography, transesophageal echocardiograpy, transthoracic echocardiography, epicardiac echocardiography, and transcutaneous or intravascular ultrasoneography in conjunction with the procedure may be used to ensure effective filtration.
  • the material of the filter screen in each embodiment of the filter catheter may be made of or coated with an adherent material or substance to capture or hold embolic debris which comes into contact with the filter screen within the valve-filter assembly.
  • adherent materials include, but are not limited to, known biocompatible adhesives and bioadhesive materials or substances, which are hemocompatible and non-thrombogenic. Such material are known to those having ordinary skill in the art and are described in, among other references, U.S. Pat. No.
  • blood is filtered during cardiac surgery, in particular during percutaneous valve surgery, to protect a patient from embolization.
  • the valve-filter is positioned in the aorta between the aortic valve and the inominate branch, where it filters blood before it reaches the carotid arteries, brachiocephalic trunk, and left subclavian artery.
  • the valve contains the embolic material and foreign matter dislodged during the surgery and also provides a temporary valve for use during valve surgery.
  • Such a method may be utilized both on and off pump.
  • Such a method may also be utilized for aortic, mitral, and pulmonary valve surgery and repair.
  • the present invention also provides for the delivery and implantation of the valve assemblies at a desired location.
  • a balloon-expandable valve delivery system permits the delivery and implantation of expandable replacement valve assemblies without the concomitant blockage of the blood flow when the balloon is fully inflated.
  • the expansion device may temporarily block the continued blood flow when the device is in its fully expanded state. Although this blockage is temporary, it exerts high pressure and stress within the heart, especially during systole. This is because the heart is essentially pumping against itself.
  • the high pressures produced from the blocked blood flow may interfere with the implantation of the replacement valve at its intended location.
  • the embodiments disclosed herein permit for the expansion of the replacement valve assemblies without blocking the flow of blood.
  • a balloon-expandable valve delivery and implantation system comprising an inflatable balloon member (1002) disposed around a catheter (1004).
  • the catheter comprises an inner lumen (1006) and a plurality of openings (1007) at the proximal (1007A) and distal (1007B) ends of the inflatable balloon member (1002).
  • the plurality of openings (1007) permits the continued blood flow in through and out of the lumen (1006) of the catheter (1004) when the balloon member (1002) is fully inflated to implant the replacement valve (1008).
  • the balloon member (1002) may be configured such that it is in fluid communication with a liquid or gas reservoir such that the balloon member (1002) may be inflated as the liquid or gas is infused from the reservoir to the balloon member and the balloon member (1002) may be contracted as the liquid or gas is withdrawn from the balloon member and back into the reservoir.
  • the balloon-expandable valve delivery and implantation system may comprise a one-way check valve within the lumen (1006) of the catheter (1004).
  • This one-way check valve acts as a temporary valve when the native valve ceases the function as is the case when the native valve leaflets are removed or compressed against the walls of the vessel as the inflatable balloon member (1002) is expanded.
  • the perfusion balloon catheter may further comprise an elongated shaft (1010) that is movably disposed within the lumen of the catheter. Because the catheter (1004) is hollow, insertion of the elongated shaft (1010) is permitted, as well as other devices used in connection with valve replacement procedures, such as distal embolic protection assemblies. When the elongated shaft (1010) is positioned in the lumen (1006) of the catheter (1004) it will prevent the formation of air pockets within the lumen (1006) of the catheter (1004) as it is inserted into and advanced through the body. The elongated shaft (1010) also prevents back flow of blood out of the catheter (1004) as the device is being advanced through the body to its intended location. When the replacement valve (1008) disposed around the balloon member (1002) is positioned at the desired location for implantation, the elongated shaft (1010) may be withdrawn from the elongated catheter (1004) to permit blood to flow through the openings (1007).
  • balloon-expandable valve delivery and implantation devices may be used to deliver and implant an expandable valve assembly either by insertion of the device through major vessels or through the apex of the heart.
  • the inflatable balloon member (1002) is first deflated and a replacement valve assembly (1008) is compressed around the deflated balloon member (1002).
  • the elongated shaft (1010) is positioned within the catheter (1004) such that it prevents the introduction of air pockets or the back flow of blood out of the catheter (1004).
  • the catheter may then be introduced into the patient through a major vessel or the apex of the heart and advanced through the vasculature to the location at which implantation of the replacement valve is desired.
  • the elongated shaft (1010) may be withdrawn or retracted to permit the blood to flow through the proximal openings (1007A), through the lumen of the catheter (1004) and out of the distal openings (1007B).
  • the balloon member (1002) may then be inflated by the infusion of fluid or other suitable medium into the balloon member.
  • the balloon member (1002) may be expanded to a diameter that is slightly larger than the diameter at the place of implantation so as to ensure that the valve is securely implanted.
  • the catheter may be used to deliver other devices, tools or fluids which may be used in connection with the implantation of replacement valve assemblies.
  • devices and tools may include imaging probes, distal embolic protection assemblies, temporary valves, valve decalcification systems, and additional balloons.
  • the balloon-expandable valve delivery and implantation system may comprise a cylindrically-shaped inflatable balloon member having a central opening.
  • the cylindrically-shaped inflatable balloon member may be deliverable to the desired location by a guide wire or a catheter.
  • Figures 51A through 57I are cross-sectional views of embodiments of the cylindrically-shaped inflatable balloon member.
  • the inflatable and substantially cylindrical balloon member (1012) comprises an outer surface (1014), an inner surface (1016) and an opening (1018) defined by the inner surface (1016) of the cylindrical balloon member (1012).
  • the opening (1018) permits blood to flow through the balloon when it is fully inflated.
  • the inflatable balloon member (1012) may further comprise one or more lumens (1020).
  • the lumen (1020) may be provided at various locations within the balloon member (1012) as depicted in FIGS. 57A through I .
  • the lumen (1020) may accommodate a guide wire or other device to position the balloon member (1012) at the desired location.
  • the lumen (1020) may be glued or attached to the inside wall (1016) of the balloon member (1012) or it may be molded to the inner surface (1016) of the balloon member (1012). Alternatively, as shown in FIG.
  • the lumen may be held in suspension within the opening (1018) of the balloon member (1012) by a plurality of arms (1020) that extend radially from the lumen to the inner surface (1016) of the balloon member (1012) to the lumen (1020).
  • the lumen described in the aforementioned embodiments and as used herein may be hollow or solid.
  • a solid or hollow lumen may be provided as a support spine to ensure that the balloon member maintains its substantially shape and is not compressed along Its longitudinal axis.
  • the lumen may be hollow so as to accommodate a guide wire that is disposed either fixedly or movably within the lumen. In this manner, the guide wire may facilitate the insertion and advancement of the balloon member to its desired location for deployment.
  • the lumen may be configured such that it is in fluid communication with a liquid or gas reservoir such that the balloon member may be inflated as the liquid or gas is infused from the reservoir to the balloon member and contracted as the liquid or gas is withdrawn from the balloon member and back into the reservoir.
  • the inner surface (1016) of the balloon member (1012) may be characterized in which the inner surface has greater tensile strength and less elasticity than the outer surface. This may be desirable such that when the replacement valve is collapsed around the balloon member for delivery to its intended location for implantation, the expansion of the valve assembly by inflation of the balloon assembly does not result in the inner surface (1016) of the balloon member (1012) from bulging inwards as a result of the high pressure involved in the radial expansion of the balloon member and the valve assembly.
  • the embodiments disclosed above may be used to deliver and implant an expandable valve assembly either by insertion of the device through major vessels or through the apex of the heart.
  • the inflatable balloon member is first deflated and a replacement valve assembly is compressed around the deflated balloon member.
  • the guide wire is positioned within the lumen of the balloon member such that it permits the delivery of the compressed valve assembly on the inflatable balloon member to the desired location.
  • the guide wire may then be introduced into the patient through a major vessel or the apex of the heart and advanced through the vasculature to the location at which implantation of the replacement valve is desired.
  • the balloon member Once the replacement valve assembly is positioned and oriented in the proper position for implantation, the balloon member may be inflated by the infusion of fluid or other suitable medium into the balloon member.
  • the balloon member may be expanded to a diameter that is slightly larger than the diameter at the place of implantation so as to ensure that the valve is securely implanted. After implantation of the valve assembly is completed, the balloon member may be deflated and removed from the patient's body.
  • the present invention also provides methods and systems for imaging the native valves and surrounding tissue before, during and/or after implantation of the replacement valves.
  • the imaging system may be useful to image the aortic, mitral, tricuspid, and pulmonary valves prior to, during and after implantation of the replacement valves to ensure proper placement of the replacement valve at the desired location.
  • the imaging system may also be useful to provide an image or map of other locations in which the valve assemblies may be implanted, such as the supra-aortic location or the inferior and/or superior vena cava, as described in co-pending and co-owned patent application Serial Nos. 10/418,677 , 10/418,633 and 10/653,397 , which is incorporated herein by reference.
  • the imaging system may be used in connection with known percutaneous techniques or with apical delivery. The apical valve delivery approach is described in co-pending U.S. patent application Serial No. 10/831,770, filed April 23, 2005 and is incorporated herein by reference.
  • the imaging system is useful for aiding in the proper placement and rotational orientation of a deliverable replacement valve at a desired location.
  • a deliverable replacement valve at a desired location.
  • Certain embodiments of the replacement valve assemblies disclosed herein have structural configurations and dimensions which are specifically adapted to fit within the geometry of the aortic valve sinus, such as commissural tabs and support posts.
  • the valve assemblies may comprise commissural support posts which are configured to coincide with the natural commissural posts of the aortic sinus.
  • imaging system disclosed herein may therefore be used to visualize the placement and the three-dimensional orientation of the valve assemblies such that the commissural support posts of the valve assembly is aligned with the natural commissural posts of the aortic sinus.
  • the proper positioning and orientation of the replacement valve not only optimizes valve durability and hemodynamics, it also ensures that the position of replacement valve does not adversely interfere with the surrounding anatomy such as, for example, by blocking the coronaries.
  • imaging system is described in connection with delivery and implantation of replacement valves, it is understood that the imaging systems is not so limited. Rather, the imaging system may also be utilized in connection with other procedures in which visualization of the valve, vessel or other body cavity is desired, such as in valve removal, valve sizing, and valvuloplasty, to name a few.
  • imaging modalities may be used in connection with the imaging system.
  • IVUS intravascular ultrasound
  • two-dimensional ultrasound probes two-dimensional ultrasound probes
  • three-dimensional ultrasound probes it is understood that other suitable imaging modalities, or a combination of various other imaging modalities, may also be used in place of or in conjunction with ultrasound imaging.
  • imaging modalities include, but are not limited to, infrared (IR), ultraviolet (UV), optical coherence tomography (OCT), and magnetic resonance imaging (MRI).
  • IR infrared
  • UV ultraviolet
  • OCT optical coherence tomography
  • MRI magnetic resonance imaging
  • ultrasound imaging may be used in conjunction with Infrared imaging (IR), which is capable of providing an image of the valve and surrounding tissues through blood.
  • the imaging probe may provide differing fields of view, such as longitudinal imaging, radial imaging or a combination of both.
  • IVUS intravascular ultrasound
  • two- and three-dimensional ultrasound probes and infrared probes are capable of providing "forward-looking" or longitudinal imaging.
  • Figures 58A and 58B depict the longitudinal and radial imaging provided by the probes on an imaging and replacement valve delivery device.
  • longitudinal imaging (1057) is provided wherein the imaging probe (1056) is disposed on a catheter (1050) and is capable of capturing an image at a longitudinal field of view (1057) that is taken at an angle relative to the longitudinal axis of the catheter (1050).
  • the imaging probe (1056) depicted in Figure 58A is located at the proximal end of the inflatable balloon member (1052) on which the replacement valve (1054) is disposed.
  • the longitudinal field of view (1057) provided by the imaging probe (1056) captures an image of both the valve (1054) and the surrounding tissue.
  • radial imaging is provided wherein the imaging probe (1058) is disposed on the catheter (1050) proximal to the inflatable balloon member (1052) on which the replacement valve (1054) is disposed.
  • the imaging probe (1058) captures an image at a radial field of view (1059) taken at a substantially perpendicular angle to the longitudinal axis of the catheter (1050).
  • the imaging probe (1058) is capable of obtaining an image that is a plane or sliced volume image of the 360° area outward from the longitudinal axis of the imaging probe (1058).
  • the imaging system may also be used in conjunction with other conventional imaging technologies, such as transthoracic ultrasound probes, transesophogeal ultrasound probes, epicardial ultrasound probes, intracardiac echo, computer tomography, magnetic resonance imaging, x-ray and cinefluoroscopy.
  • imaging technologies may further assist in determining and verifying various anatomical features observed by the imaging probe and to further assist in the proper placement and orientation of replacement valve assembly.
  • radiopaque and/or sonoreflective markers may be provided at various locations within the anchor or support structure of the replacement valve to visualize the relative position of the valve assembly in the patient's body. While the use of the imaging system disclosed herein provides an image of the valve and surrounding tissues within which the replacement valve is positioned, the conventional imaging technologies may be used to provide information as to the position and orientation of the replacement valve relative to the valve and surrounding tissues.
  • the imaging system may be incorporated onto a replacement valve delivery system and used to visualize the location in which implantation of the replacement valve is desired. The imaging system may then be used to position and orient the replacement valve at the desired location during implantation and to subsequently inspect the implanted replacement valve at the desired location.
  • the imaging and valve delivery system may be used to deliver an expandable valve assembly, such as a balloon-expandable valve assembly, to a desired location.
  • the imaging and valve delivery system may generally comprises at least one imaging probe, a catheter, an inflatable balloon member disposed on the catheter, and an expandable valve assembly compressed around the inflatable balloon member.
  • the catheter may comprise openings at the distal and proximal ends of the balloon member, as described above, to permit blood to flow therethrough and to prevent the buildup of pressure when the balloon member is expanded.
  • the one or more imaging probes may be provided on various locations on the catheter.
  • a single imaging probe may be located on the catheter either just outside and adjacent to the balloon member or within the balloon member.
  • the imaging probe may provide either longitudinal or radial imaging, depending on the type of imaging probe that is used.
  • the location of the imaging probe on the catheter is selected such that it the position of the valve assembly relative to the captured image can be ascertained.
  • the imaging probe may also be located on the catheter such that it is centered directly underneath the valve assembly.
  • FIGs 59A-C depict embodiments of the imaging and replacement valve delivery system, wherein a single imaging probe is provided at various locations on the catheter.
  • the imaging and replacement valve delivery systems in Figures 59A-C comprise a delivery catheter (1060) having an inflatable balloon member (1064) disposed around the catheter (1060).
  • An expandable valve assembly (1066) is shown in the fully expanded state and disposed around the fully inflated balloon member (1064).
  • the imaging probe (1062) is provided on the catheter (1060) at a fixed location within the balloon member (1064) and underneath the valve assembly (1066) such that it is capable of capturing an image of the 360° area (1063) surrounding the replacement valve assembly (1066).
  • the imaging probe (1062) is provided on the catheter (1060) at a fixed location inside the balloon member (1064) and adjacent one side of the valve assembly (1066) such that it is capable of capturing an image of the 360° area (1063) adjacent the replacement valve assembly (1066).
  • multiple imaging probes may be provided in a variety of configurations.
  • two imaging probes (1082, 1084) may be provided at fixed locations on the catheter (1080) such that they are located adjacent to either the ends of the valve assembly (1088) to provide an images of the 360° area (1083, 1085) adjacent both ends of the replacement valve assembly (1066).
  • a third imaging probe (1090) may be provided on the catheter (1080) at a fixed location within the balloon member (1086) and underneath the valve assembly (1088) such that it is capable of capturing an image of the 360° area (1091) surrounding the replacement valve assembly (1088).
  • Figure 60C depicts an alternate embodiment in which two imaging probes (1082, 1084) may be provided at a fixed location on the catheter (1080) such that they are located adjacent to either the ends of the balloon member (1086) to provide an images of the 360° area (1083, 1085) adjacent both ends of the balloon member (1086).
  • the number or location of the imaging probes on the catheter is not critical so long as the relative position of the imaging probe and the compressed valve assembly is known so as to permit precise placement of the replacement valve assembly at its desired location within the valve or other body cavity. It is also understood that while the figures depict the radial field of view provided by the imaging probes, it is not so limited. A variety of different imaging probes may be provided on a single catheter having varying fields of view, including the longitudinal field of view disclosed herein.
  • the imaging system may also be used in connection with visualization of the valve or vessel and its surrounding tissue prior to valvuloplasty. Accordingly, the imaging system may be used to visualize the valve or vessel for calcification or other lesions and the balloon member may be inflated to compress or remove the calcium deposits or lesions.
  • the valvuloplasty imaging system is similar to the imaging and replacement valve system described above, with the exception that the replacement valve assembly is not included.
  • a distal embolic protection assembly may be delivered through the catheter and deployed downstream prior to inflation of the balloon member once a stenosed valve or vessel is diagnosed using the imaging system and identified as suitable for valvuloplasty. Suitable distal embolic protection assemblies are generally known and also disclosed in co-pending and co-owned patent application Serial No. 10/938,410, filed September 10, 2004 .
  • the replacement valve system comprises an apparatus for the delivery of a self-expandable valve assembly and an imaging system.
  • the imaging and replacement valve delivery system comprises a catheter (1100), a self-expandable valve assembly (1104) compressed around the catheter (1100) and a sleeve (1102) movably disposed on the catheter (1100) to maintain the self-expandable valve (1104) in a compressed state for delivery of the valve to a desired location.
  • the one or more imaging probes may be provided on the catheter for the imaging and replacement valve delivery system for the expandable valves.
  • the imaging probe (1110) is located on the catheter (1100) at a fixed location underneath the self-expandable valve (1104) to provide an image of the 360° area (1111) surrounding the self-expandable valve (1104).
  • the imaging probe (1112) is located on the catheter (1100) at a fixed location proximal to the self-expandable valve (1104) to provide an image of the longitudinal field of view (1113) surrounding the self-expandable valve (1104).
  • the imaging probe is depicted in Figures 61A-B as being located on the catheter, in yet a further embodiment, the one or more imaging probes may be provided on the outside of the sleeve (1102), such that the location in which implantation of the valve assembly (1104) is visualized and the relative position of the imaging probe(s) (1110, 1112) and the compressed valve (1104) is known.
  • the imaging probe may be separately provided such that it is inserted into the lumen of the catheter and movably disposed within the lumen catheter in connection with the delivery of either the balloon expandable valve or the self-expandable valve.
  • the imaging probe may be used to provide a complete picture of how the valve assembly is positioned relative to certain anatomical structures at the desired location just prior to deployment of the valve assembly.
  • the imaging system may be used to inspect the position of the valve assembly.
  • a movable imaging probe (1200) is provided within the lumen of the catheter (1202) having an inflatable balloon member (1204) disposed therein.
  • the replacement valve (1206) is provided around the inflatable balloon (1204) such that it may be expanded at a desired location.
  • imaging probe (1200) may provide either radial or longitudinal fields of view (not shown).
  • a method and assembly in which the placement of the replacement heart valve is accomplished by providing either a two- or three-dimensional map of the target location and surrounding tissue in which placement of the replacement heart valve is desired. Once such a map of the target location is generated, the replacement valve assembly may then be delivered and positioned at the target location by reference to the map of the

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EP14163073.1A 2003-10-06 2004-10-06 Systeme de remplacement valvulaire minimalement invasif Expired - Lifetime EP2789314B1 (fr)

Applications Claiming Priority (16)

Application Number Priority Date Filing Date Title
US10/680,069 US20050075729A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,071 US7101396B2 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,716 US20050075718A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,717 US20050075719A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,560 US20050075717A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,567 US20050096738A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,733 US20050075584A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,728 US20050075713A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,732 US20050075720A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,562 US20050075724A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,068 US7044966B2 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,719 US20050075712A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,075 US20050075728A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US10/680,070 US20050075730A1 (en) 2003-10-06 2003-10-06 Minimally invasive valve replacement system
US52924203P 2003-12-12 2003-12-12
EP04794398.0A EP1684671B1 (fr) 2003-10-06 2004-10-06 Systeme de remplacement valvulaire minimalement effractif

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2789314B1 (fr) 2003-10-06 2018-04-25 Medtronic 3F Therapeutics, Inc. Systeme de remplacement valvulaire minimalement invasif
EP3583920B1 (fr) 2011-07-15 2020-06-17 Edwards Lifesciences Corporation Armature de valvule prothétique
US11123184B2 (en) 2010-10-05 2021-09-21 Edwards Lifesciences Corporation Prosthetic heart valve
US11129710B2 (en) 2011-12-09 2021-09-28 Edwards Lifesciences Corporation Prosthetic heart valve having improved commissure supports
WO2022159431A1 (fr) * 2021-01-20 2022-07-28 Edwards Lifesciences Corporation Dispositif d'amarrage bi-caval extensible mécaniquement

Families Citing this family (704)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6006134A (en) 1998-04-30 1999-12-21 Medtronic, Inc. Method and device for electronically controlling the beating of a heart using venous electrical stimulation of nerve fibers
US6530952B2 (en) 1997-12-29 2003-03-11 The Cleveland Clinic Foundation Bioprosthetic cardiovascular valve system
US7018406B2 (en) 1999-11-17 2006-03-28 Corevalve Sa Prosthetic valve for transluminal delivery
US8016877B2 (en) 1999-11-17 2011-09-13 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8579966B2 (en) 1999-11-17 2013-11-12 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US6692513B2 (en) 2000-06-30 2004-02-17 Viacor, Inc. Intravascular filter with debris entrapment mechanism
US7749245B2 (en) 2000-01-27 2010-07-06 Medtronic, Inc. Cardiac valve procedure methods and devices
US8366769B2 (en) 2000-06-01 2013-02-05 Edwards Lifesciences Corporation Low-profile, pivotable heart valve sewing ring
EP1408997A2 (fr) * 2000-06-16 2004-04-21 McGILL UNIVERSITY Extrait de kefir utilise comme agent anticancereux
US6409758B2 (en) * 2000-07-27 2002-06-25 Edwards Lifesciences Corporation Heart valve holder for constricting the valve commissures and methods of use
JP2004506469A (ja) 2000-08-18 2004-03-04 アトリテック, インコーポレイテッド 心耳からの血流をろ過するための拡張可能な埋め込みデバイス
US6602286B1 (en) 2000-10-26 2003-08-05 Ernst Peter Strecker Implantable valve system
US8038708B2 (en) 2001-02-05 2011-10-18 Cook Medical Technologies Llc Implantable device with remodelable material and covering material
US8623077B2 (en) 2001-06-29 2014-01-07 Medtronic, Inc. Apparatus for replacing a cardiac valve
US8771302B2 (en) 2001-06-29 2014-07-08 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US7544206B2 (en) 2001-06-29 2009-06-09 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
FR2826863B1 (fr) 2001-07-04 2003-09-26 Jacques Seguin Ensemble permettant la mise en place d'une valve prothetique dans un conduit corporel
FR2828091B1 (fr) 2001-07-31 2003-11-21 Seguin Jacques Ensemble permettant la mise en place d'une valve prothetique dans un conduit corporel
US7097659B2 (en) 2001-09-07 2006-08-29 Medtronic, Inc. Fixation band for affixing a prosthetic heart valve to tissue
US20060292206A1 (en) 2001-11-26 2006-12-28 Kim Steven W Devices and methods for treatment of vascular aneurysms
US7201771B2 (en) 2001-12-27 2007-04-10 Arbor Surgical Technologies, Inc. Bioprosthetic heart valve
US6752828B2 (en) 2002-04-03 2004-06-22 Scimed Life Systems, Inc. Artificial valve
US7125418B2 (en) * 2002-04-16 2006-10-24 The International Heart Institute Of Montana Foundation Sigmoid valve and method for its percutaneous implantation
US8721713B2 (en) 2002-04-23 2014-05-13 Medtronic, Inc. System for implanting a replacement valve
US7959674B2 (en) 2002-07-16 2011-06-14 Medtronic, Inc. Suture locking assembly and method of use
US7481821B2 (en) 2002-11-12 2009-01-27 Thomas J. Fogarty Embolization device and a method of using the same
US7766973B2 (en) * 2005-01-19 2010-08-03 Gi Dynamics, Inc. Eversion resistant sleeves
US8551162B2 (en) 2002-12-20 2013-10-08 Medtronic, Inc. Biologically implantable prosthesis
US6945957B2 (en) 2002-12-30 2005-09-20 Scimed Life Systems, Inc. Valve treatment catheter and methods
US20040260382A1 (en) 2003-02-12 2004-12-23 Fogarty Thomas J. Intravascular implants and methods of using the same
CH696185A5 (fr) * 2003-03-21 2007-02-15 Afksendiyos Kalangos Dispositif de renfort intraparietal pour prothèse biologique et prothèse biologique renforcée.
US7658759B2 (en) * 2003-04-24 2010-02-09 Cook Incorporated Intralumenally implantable frames
EP2926772A1 (fr) 2003-04-24 2015-10-07 Cook Medical Technologies LLC Prothèse artificielle de valvule dont la dynamique d'écoulement est améliorée
US7625399B2 (en) 2003-04-24 2009-12-01 Cook Incorporated Intralumenally-implantable frames
US7717952B2 (en) * 2003-04-24 2010-05-18 Cook Incorporated Artificial prostheses with preferred geometries
JP4942031B2 (ja) * 2003-07-08 2012-05-30 メドトロニック ベンター テクノロジーズ リミティド 特に大動脈弁狭窄症の治療における経動脈的デリバリに適した移植可能な人工補綴装置、及び同人工補綴装置を移植する方法
US7201772B2 (en) * 2003-07-08 2007-04-10 Ventor Technologies, Ltd. Fluid flow prosthetic device
US20050015110A1 (en) 2003-07-18 2005-01-20 Fogarty Thomas J. Embolization device and a method of using the same
ATE442107T1 (de) * 2003-07-21 2009-09-15 Univ Pennsylvania Perkutane herzklappe
FR2858543B1 (fr) * 2003-08-08 2006-02-03 Assist Publ Hopitaux De Paris Anneau aortique et ancillaire pour sa pose
US8021421B2 (en) 2003-08-22 2011-09-20 Medtronic, Inc. Prosthesis heart valve fixturing device
US7842084B2 (en) * 2005-06-21 2010-11-30 3F Therapeutics, Inc. Method and systems for sizing, folding, holding, and delivering a heart valve prosthesis
US10219899B2 (en) * 2004-04-23 2019-03-05 Medtronic 3F Therapeutics, Inc. Cardiac valve replacement systems
US7604650B2 (en) * 2003-10-06 2009-10-20 3F Therapeutics, Inc. Method and assembly for distal embolic protection
US9579194B2 (en) 2003-10-06 2017-02-28 Medtronic ATS Medical, Inc. Anchoring structure with concave landing zone
US20060259137A1 (en) * 2003-10-06 2006-11-16 Jason Artof Minimally invasive valve replacement system
US7556647B2 (en) 2003-10-08 2009-07-07 Arbor Surgical Technologies, Inc. Attachment device and methods of using the same
US7854761B2 (en) 2003-12-19 2010-12-21 Boston Scientific Scimed, Inc. Methods for venous valve replacement with a catheter
US8128681B2 (en) 2003-12-19 2012-03-06 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
EP1703870B1 (fr) * 2003-12-19 2019-05-01 Patrick Leahy Systeme anti-reflux
US7748389B2 (en) 2003-12-23 2010-07-06 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US8287584B2 (en) 2005-11-14 2012-10-16 Sadra Medical, Inc. Medical implant deployment tool
US7329279B2 (en) 2003-12-23 2008-02-12 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US7824443B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Medical implant delivery and deployment tool
US8579962B2 (en) 2003-12-23 2013-11-12 Sadra Medical, Inc. Methods and apparatus for performing valvuloplasty
US20050137686A1 (en) * 2003-12-23 2005-06-23 Sadra Medical, A Delaware Corporation Externally expandable heart valve anchor and method
US9526609B2 (en) 2003-12-23 2016-12-27 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US7780725B2 (en) 2004-06-16 2010-08-24 Sadra Medical, Inc. Everting heart valve
US8828078B2 (en) 2003-12-23 2014-09-09 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8182528B2 (en) 2003-12-23 2012-05-22 Sadra Medical, Inc. Locking heart valve anchor
US7959666B2 (en) 2003-12-23 2011-06-14 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US20050137694A1 (en) * 2003-12-23 2005-06-23 Haug Ulrich R. Methods and apparatus for endovascularly replacing a patient's heart valve
US8840663B2 (en) 2003-12-23 2014-09-23 Sadra Medical, Inc. Repositionable heart valve method
US20120041550A1 (en) 2003-12-23 2012-02-16 Sadra Medical, Inc. Methods and Apparatus for Endovascular Heart Valve Replacement Comprising Tissue Grasping Elements
AU2004308508B2 (en) 2003-12-23 2011-03-10 Sadra Medical, Inc. Repositionable heart valve
US8603160B2 (en) 2003-12-23 2013-12-10 Sadra Medical, Inc. Method of using a retrievable heart valve anchor with a sheath
US20050137687A1 (en) 2003-12-23 2005-06-23 Sadra Medical Heart valve anchor and method
US8343213B2 (en) 2003-12-23 2013-01-01 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US11278398B2 (en) 2003-12-23 2022-03-22 Boston Scientific Scimed, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US7381219B2 (en) 2003-12-23 2008-06-03 Sadra Medical, Inc. Low profile heart valve and delivery system
US7824442B2 (en) * 2003-12-23 2010-11-02 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US7445631B2 (en) 2003-12-23 2008-11-04 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US9005273B2 (en) 2003-12-23 2015-04-14 Sadra Medical, Inc. Assessing the location and performance of replacement heart valves
US8328868B2 (en) 2004-11-05 2012-12-11 Sadra Medical, Inc. Medical devices and delivery systems for delivering medical devices
US7871435B2 (en) 2004-01-23 2011-01-18 Edwards Lifesciences Corporation Anatomically approximate prosthetic mitral heart valve
CN101683291A (zh) * 2004-02-27 2010-03-31 奥尔特克斯公司 人工心脏瓣膜传送系统和方法
US20070073387A1 (en) * 2004-02-27 2007-03-29 Forster David C Prosthetic Heart Valves, Support Structures And Systems And Methods For Implanting The Same
ITTO20040135A1 (it) 2004-03-03 2004-06-03 Sorin Biomedica Cardio Spa Protesi valvolare cardiaca
EP1734903B2 (fr) 2004-03-11 2022-01-19 Percutaneous Cardiovascular Solutions Pty Limited Prothese de valvule cardiaque percutanee
US20050228494A1 (en) * 2004-03-29 2005-10-13 Salvador Marquez Controlled separation heart valve frame
US8349001B2 (en) * 2004-04-07 2013-01-08 Medtronic, Inc. Pharmacological delivery implement for use with cardiac repair devices
US7637937B2 (en) * 2004-04-08 2009-12-29 Cook Incorporated Implantable medical device with optimized shape
US20060025857A1 (en) 2004-04-23 2006-02-02 Bjarne Bergheim Implantable prosthetic valve
US20060122692A1 (en) * 2004-05-10 2006-06-08 Ran Gilad Stent valve and method of using same
US20060122686A1 (en) * 2004-05-10 2006-06-08 Ran Gilad Stent and method of manufacturing same
US20060122693A1 (en) * 2004-05-10 2006-06-08 Youssef Biadillah Stent valve and method of manufacturing same
US7276078B2 (en) * 2004-06-30 2007-10-02 Edwards Lifesciences Pvt Paravalvular leak detection, sealing, and prevention
US7566343B2 (en) 2004-09-02 2009-07-28 Boston Scientific Scimed, Inc. Cardiac valve, system, and method
FR2874813B1 (fr) * 2004-09-07 2007-06-22 Perouse Soc Par Actions Simpli Prothese valvulaire
US20060052867A1 (en) 2004-09-07 2006-03-09 Medtronic, Inc Replacement prosthetic heart valve, system and method of implant
EP1796597B1 (fr) * 2004-09-14 2013-01-09 Edwards Lifesciences AG Dispositif de traitement de la régurgitation valvulaire
US7331010B2 (en) * 2004-10-29 2008-02-12 International Business Machines Corporation System, method and storage medium for providing fault detection and correction in a memory subsystem
US8562672B2 (en) 2004-11-19 2013-10-22 Medtronic, Inc. Apparatus for treatment of cardiac valves and method of its manufacture
US7744642B2 (en) * 2004-11-19 2010-06-29 Biomedical Research Associates, Inc. Prosthetic venous valves
WO2006060546A2 (fr) * 2004-12-01 2006-06-08 Cook Incorporated Dispositif medical a voie de fuite
US7758640B2 (en) * 2004-12-16 2010-07-20 Valvexchange Inc. Cardiovascular valve assembly
DE102005003632A1 (de) 2005-01-20 2006-08-17 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Katheter für die transvaskuläre Implantation von Herzklappenprothesen
US7854755B2 (en) 2005-02-01 2010-12-21 Boston Scientific Scimed, Inc. Vascular catheter, system, and method
US20060173490A1 (en) 2005-02-01 2006-08-03 Boston Scientific Scimed, Inc. Filter system and method
US7878966B2 (en) 2005-02-04 2011-02-01 Boston Scientific Scimed, Inc. Ventricular assist and support device
US7780722B2 (en) 2005-02-07 2010-08-24 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
US7670368B2 (en) 2005-02-07 2010-03-02 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
US8574257B2 (en) * 2005-02-10 2013-11-05 Edwards Lifesciences Corporation System, device, and method for providing access in a cardiovascular environment
ITTO20050074A1 (it) 2005-02-10 2006-08-11 Sorin Biomedica Cardio Srl Protesi valvola cardiaca
US7867274B2 (en) 2005-02-23 2011-01-11 Boston Scientific Scimed, Inc. Valve apparatus, system and method
US7331991B2 (en) * 2005-02-25 2008-02-19 California Institute Of Technology Implantable small percutaneous valve and methods of delivery
WO2006092648A1 (fr) * 2005-03-01 2006-09-08 Leman Cardiovascular Sa Dispositif de renfort intraparietal pour prothese cardiaque biologique et prothese cardiaque biologique renforcee
WO2006097931A2 (fr) 2005-03-17 2006-09-21 Valtech Cardio, Ltd. Techniques de traitement de la valve mitrale
US7513909B2 (en) 2005-04-08 2009-04-07 Arbor Surgical Technologies, Inc. Two-piece prosthetic valves with snap-in connection and methods for use
US7722666B2 (en) 2005-04-15 2010-05-25 Boston Scientific Scimed, Inc. Valve apparatus, system and method
SE531468C2 (sv) 2005-04-21 2009-04-14 Edwards Lifesciences Ag En anordning för styrning av blodflöde
US8333777B2 (en) 2005-04-22 2012-12-18 Benvenue Medical, Inc. Catheter-based tissue remodeling devices and methods
US7962208B2 (en) 2005-04-25 2011-06-14 Cardiac Pacemakers, Inc. Method and apparatus for pacing during revascularization
US7914569B2 (en) 2005-05-13 2011-03-29 Medtronics Corevalve Llc Heart valve prosthesis and methods of manufacture and use
WO2006127756A2 (fr) 2005-05-24 2006-11-30 Edwards Lifesciences Corporation Prothese de valvule cardiaque a deploiement rapide
EP1895942B1 (fr) 2005-05-27 2020-05-13 Medtronic, Inc. Joint a collier pour valves cardiaques prothetiques
WO2006128193A2 (fr) 2005-05-27 2006-11-30 Heart Leaflet Technologies, Inc. Structure support sans stent
US7955372B2 (en) * 2005-06-01 2011-06-07 Board Of Trustees Of The Leland Stanford Junior University Endoluminal delivery system
US8012198B2 (en) 2005-06-10 2011-09-06 Boston Scientific Scimed, Inc. Venous valve, system, and method
US7780723B2 (en) * 2005-06-13 2010-08-24 Edwards Lifesciences Corporation Heart valve delivery system
US8951285B2 (en) 2005-07-05 2015-02-10 Mitralign, Inc. Tissue anchor, anchoring system and methods of using the same
US7682391B2 (en) * 2005-07-13 2010-03-23 Edwards Lifesciences Corporation Methods of implanting a prosthetic mitral heart valve having a contoured sewing ring
US20080269879A1 (en) * 2005-07-27 2008-10-30 Rahul Dilip Sathe Implantable Prosthetic Vascular Valve
US8790396B2 (en) * 2005-07-27 2014-07-29 Medtronic 3F Therapeutics, Inc. Methods and systems for cardiac valve delivery
US7455689B2 (en) 2005-08-25 2008-11-25 Edwards Lifesciences Corporation Four-leaflet stented mitral heart valve
US7712606B2 (en) 2005-09-13 2010-05-11 Sadra Medical, Inc. Two-part package for medical implant
US7569071B2 (en) 2005-09-21 2009-08-04 Boston Scientific Scimed, Inc. Venous valve, system, and method with sinus pocket
WO2007038540A1 (fr) 2005-09-26 2007-04-05 Medtronic, Inc. Valve cardiaque prothétique et valvules veineuses
US8167932B2 (en) 2005-10-18 2012-05-01 Edwards Lifesciences Corporation Heart valve delivery system with valve catheter
GB0521582D0 (en) * 2005-10-22 2005-11-30 Depuy Int Ltd An implant for supporting a spinal column
GB0521585D0 (en) * 2005-10-22 2005-11-30 Depuy Int Ltd A spinal support rod
EP3167847B1 (fr) 2005-11-10 2020-10-14 Edwards Lifesciences CardiAQ LLC Prothèse cardiaque
US8764820B2 (en) 2005-11-16 2014-07-01 Edwards Lifesciences Corporation Transapical heart valve delivery system and method
WO2007100408A2 (fr) * 2005-12-15 2007-09-07 Georgia Tech Research Corporation dispositifs, SYSTÈMES, & PROCÉDÉS de commande de position de muscle papillaire
EP1968492A2 (fr) * 2005-12-15 2008-09-17 Georgia Technology Research Corporation SYSTÉMES ET PROCÉDÉS POUR CONTROLÉR lES DIMESIONS D'UNE VALVE CARDIAQUE
WO2007100410A2 (fr) * 2005-12-15 2007-09-07 Georgia Tech Research Corporation systèmes et procédés permettant le remplacement d'une valve cardiaque
US20070142907A1 (en) * 2005-12-16 2007-06-21 Micardia Corporation Adjustable prosthetic valve implant
US20070213813A1 (en) 2005-12-22 2007-09-13 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
US9078781B2 (en) 2006-01-11 2015-07-14 Medtronic, Inc. Sterile cover for compressible stents used in percutaneous device delivery systems
GB0600662D0 (en) * 2006-01-13 2006-02-22 Depuy Int Ltd Spinal support rod kit
US7799038B2 (en) 2006-01-20 2010-09-21 Boston Scientific Scimed, Inc. Translumenal apparatus, system, and method
US8348952B2 (en) * 2006-01-26 2013-01-08 Depuy International Ltd. System and method for cooling a spinal correction device comprising a shape memory material for corrective spinal surgery
US7967857B2 (en) 2006-01-27 2011-06-28 Medtronic, Inc. Gasket with spring collar for prosthetic heart valves and methods for making and using them
WO2007097983A2 (fr) 2006-02-14 2007-08-30 Sadra Medical, Inc. Systemes et procedes pour installer un implant medical
WO2008029296A2 (fr) * 2006-02-16 2008-03-13 Endocor Pte Ltd. Remplacement d'une valvule cardiaque en une chirurgie mini-invasive
US7780724B2 (en) * 2006-02-24 2010-08-24 California Institute Of Technology Monolithic in situ forming valve system
US20080275550A1 (en) * 2006-02-24 2008-11-06 Arash Kheradvar Implantable small percutaneous valve and methods of delivery
US8147541B2 (en) 2006-02-27 2012-04-03 Aortx, Inc. Methods and devices for delivery of prosthetic heart valves and other prosthetics
US7749266B2 (en) * 2006-02-27 2010-07-06 Aortx, Inc. Methods and devices for delivery of prosthetic heart valves and other prosthetics
WO2007123658A1 (fr) 2006-03-28 2007-11-01 Medtronic, Inc. Valvule cardiaque prothétique constituée de matière péricardique et procédés de production de cette valvule
US7740655B2 (en) 2006-04-06 2010-06-22 Medtronic Vascular, Inc. Reinforced surgical conduit for implantation of a stented valve therein
US7591848B2 (en) * 2006-04-06 2009-09-22 Medtronic Vascular, Inc. Riveted stent valve for percutaneous use
US20070244544A1 (en) 2006-04-14 2007-10-18 Medtronic Vascular, Inc. Seal for Enhanced Stented Valve Fixation
US8551161B2 (en) 2006-04-25 2013-10-08 Medtronic Vascular, Inc. Cardiac valve annulus restraining device
EP2012712B1 (fr) 2006-04-29 2016-02-10 Medtronic, Inc. Guides pour des valves cardiaques prosthétiques à composants multiples
EP2023860A2 (fr) 2006-04-29 2009-02-18 Arbor Surgical Technologies, Inc. Ensembles de valves cardiaques prosthétiques à composants multiples et appareil et procédés pour leur implantation
US8021161B2 (en) 2006-05-01 2011-09-20 Edwards Lifesciences Corporation Simulated heart valve root for training and testing
US8932348B2 (en) 2006-05-18 2015-01-13 Edwards Lifesciences Corporation Device and method for improving heart valve function
US8585594B2 (en) 2006-05-24 2013-11-19 Phoenix Biomedical, Inc. Methods of assessing inner surfaces of body lumens or organs
CN102283721B (zh) 2006-06-01 2015-08-26 爱德华兹生命科学公司 用于改善心瓣膜功能的人工插入物
CN101505686A (zh) 2006-06-20 2009-08-12 奥尔特克斯公司 人造心脏瓣膜、支撑结构以及用于植入该人造心脏瓣膜及支撑结构的系统和方法
JP2009540954A (ja) * 2006-06-20 2009-11-26 エーオーテックス, インコーポレイテッド 補綴弁移植部位の調製技術
WO2007149841A2 (fr) 2006-06-20 2007-12-27 Aortx, Inc. Arbre de torsion et transmission de couple
JP2009540956A (ja) * 2006-06-21 2009-11-26 エーオーテックス, インコーポレイテッド 補綴弁移植システム
US20080004696A1 (en) * 2006-06-29 2008-01-03 Valvexchange Inc. Cardiovascular valve assembly with resizable docking station
US20080126131A1 (en) * 2006-07-17 2008-05-29 Walgreen Co. Predictive Modeling And Risk Stratification Of A Medication Therapy Regimen
WO2008013915A2 (fr) * 2006-07-28 2008-01-31 Arshad Quadri Prothèse à valve percutanée et système et procédé pour implanter une telle prothèse
US9408607B2 (en) * 2009-07-02 2016-08-09 Edwards Lifesciences Cardiaq Llc Surgical implant devices and methods for their manufacture and use
US9585743B2 (en) 2006-07-31 2017-03-07 Edwards Lifesciences Cardiaq Llc Surgical implant devices and methods for their manufacture and use
WO2008016578A2 (fr) 2006-07-31 2008-02-07 Cartledge Richard G Implants endovasculaires scellables et leurs procédés d'utilisation
GB0617219D0 (en) 2006-08-31 2006-10-11 Barts & London Nhs Trust Blood vessel prosthesis and delivery apparatus
EP1978895B1 (fr) 2006-09-08 2010-06-09 Edwards Lifesciences Corporation Système intégré de transport de valvule cardiaque
US11304800B2 (en) 2006-09-19 2022-04-19 Medtronic Ventor Technologies Ltd. Sinus-engaging valve fixation member
US8834564B2 (en) 2006-09-19 2014-09-16 Medtronic, Inc. Sinus-engaging valve fixation member
US8876895B2 (en) 2006-09-19 2014-11-04 Medtronic Ventor Technologies Ltd. Valve fixation member having engagement arms
WO2008046092A2 (fr) * 2006-10-13 2008-04-17 Creighton University Prothèse de valve implantable
WO2008047354A2 (fr) 2006-10-16 2008-04-24 Ventor Technologies Ltd. Système d'administration transapicale avec dérivation de débordement ventriculo-artérielle
WO2008047368A2 (fr) * 2006-10-18 2008-04-24 Inspiremd Ltd. Ensembles filtre
US9883943B2 (en) 2006-12-05 2018-02-06 Valtech Cardio, Ltd. Implantation of repair devices in the heart
US11259924B2 (en) 2006-12-05 2022-03-01 Valtech Cardio Ltd. Implantation of repair devices in the heart
AU2007329243B2 (en) 2006-12-06 2014-04-03 Medtronic CV Luxembourg S.a.r.l System and method for transapical delivery of an annulus anchored self-expanding valve
US8070799B2 (en) * 2006-12-19 2011-12-06 Sorin Biomedica Cardio S.R.L. Instrument and method for in situ deployment of cardiac valve prostheses
US8470024B2 (en) 2006-12-19 2013-06-25 Sorin Group Italia S.R.L. Device for in situ positioning of cardiac valve prosthesis
US9192471B2 (en) 2007-01-08 2015-11-24 Millipede, Inc. Device for translumenal reshaping of a mitral valve annulus
US20100249920A1 (en) * 2007-01-08 2010-09-30 Millipede Llc Reconfiguring heart features
US8133270B2 (en) 2007-01-08 2012-03-13 California Institute Of Technology In-situ formation of a valve
US20100168844A1 (en) * 2007-01-26 2010-07-01 3F Therapeutics, Inc. Methods and systems for reducing paravalvular leakage in heart valves
WO2008097589A1 (fr) 2007-02-05 2008-08-14 Boston Scientific Limited Valve percutanée, système et procédé
WO2008103280A2 (fr) 2007-02-16 2008-08-28 Medtronic, Inc. Systèmes de mise en place et méthodes d'implantation de prothèses de valves cardiaques
US8070802B2 (en) * 2007-02-23 2011-12-06 The Trustees Of The University Of Pennsylvania Mitral valve system
US7753949B2 (en) * 2007-02-23 2010-07-13 The Trustees Of The University Of Pennsylvania Valve prosthesis systems and methods
US11660190B2 (en) 2007-03-13 2023-05-30 Edwards Lifesciences Corporation Tissue anchors, systems and methods, and devices
US7896915B2 (en) * 2007-04-13 2011-03-01 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
FR2915087B1 (fr) 2007-04-20 2021-11-26 Corevalve Inc Implant de traitement d'une valve cardiaque, en particulier d'une valve mitrale, materiel inculant cet implant et materiel de mise en place de cet implant.
US20080294248A1 (en) * 2007-05-25 2008-11-27 Medical Entrepreneurs Ii, Inc. Prosthetic Heart Valve
US7815677B2 (en) * 2007-07-09 2010-10-19 Leman Cardiovascular Sa Reinforcement device for a biological valve and reinforced biological valve
US8663318B2 (en) * 2007-07-23 2014-03-04 Hocor Cardiovascular Technologies Llc Method and apparatus for percutaneous aortic valve replacement
US8663319B2 (en) 2007-07-23 2014-03-04 Hocor Cardiovascular Technologies Llc Methods and apparatus for percutaneous aortic valve replacement
DE102007034363A1 (de) * 2007-07-24 2009-01-29 Biotronik Vi Patent Ag Endoprothese
US8828079B2 (en) 2007-07-26 2014-09-09 Boston Scientific Scimed, Inc. Circulatory valve, system and method
US9814611B2 (en) 2007-07-31 2017-11-14 Edwards Lifesciences Cardiaq Llc Actively controllable stent, stent graft, heart valve and method of controlling same
US9566178B2 (en) 2010-06-24 2017-02-14 Edwards Lifesciences Cardiaq Llc Actively controllable stent, stent graft, heart valve and method of controlling same
US8747458B2 (en) 2007-08-20 2014-06-10 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
DE202008018551U1 (de) 2007-08-21 2015-10-26 Symetis Sa Eine Ersatzklappe
US8114154B2 (en) 2007-09-07 2012-02-14 Sorin Biomedica Cardio S.R.L. Fluid-filled delivery system for in situ deployment of cardiac valve prostheses
US8808367B2 (en) 2007-09-07 2014-08-19 Sorin Group Italia S.R.L. Prosthetic valve delivery system including retrograde/antegrade approach
US8425593B2 (en) 2007-09-26 2013-04-23 St. Jude Medical, Inc. Collapsible prosthetic heart valves
WO2009045334A1 (fr) 2007-09-28 2009-04-09 St. Jude Medical, Inc. Valvules cardiaques prothétiques repliables/déployables dotées de caractéristiques de retenue des valves natives calcifiées
US9532868B2 (en) 2007-09-28 2017-01-03 St. Jude Medical, Inc. Collapsible-expandable prosthetic heart valves with structures for clamping native tissue
US10856970B2 (en) 2007-10-10 2020-12-08 Medtronic Ventor Technologies Ltd. Prosthetic heart valve for transfemoral delivery
US9848981B2 (en) 2007-10-12 2017-12-26 Mayo Foundation For Medical Education And Research Expandable valve prosthesis with sealing mechanism
US20090105810A1 (en) 2007-10-17 2009-04-23 Hancock Jaffe Laboratories Biological valve for venous valve insufficiency
US20090105813A1 (en) * 2007-10-17 2009-04-23 Sean Chambers Implantable valve device
GB0720762D0 (en) 2007-10-24 2007-12-05 Depuy Spine Sorl Assembly for orthopaedic surgery
CA2703665C (fr) 2007-10-25 2016-05-10 Symetis Sa Stents, stents a valve et procedes et systemes de mise en place de ceux-ci
US7846199B2 (en) * 2007-11-19 2010-12-07 Cook Incorporated Remodelable prosthetic valve
US8313526B2 (en) 2007-11-19 2012-11-20 Cook Medical Technologies Llc Valve frame
PL3643273T3 (pl) 2007-12-14 2021-12-06 Edwards Lifesciences Corporation Ramka do mocowania płatka dla sztucznej zastawki
US7892276B2 (en) 2007-12-21 2011-02-22 Boston Scientific Scimed, Inc. Valve with delayed leaflet deployment
US9226813B2 (en) 2007-12-26 2016-01-05 Cook Medical Technologies Llc Low profile non-symmetrical stent
US9180030B2 (en) 2007-12-26 2015-11-10 Cook Medical Technologies Llc Low profile non-symmetrical stent
US8574284B2 (en) 2007-12-26 2013-11-05 Cook Medical Technologies Llc Low profile non-symmetrical bare alignment stents with graft
US8728145B2 (en) * 2008-12-11 2014-05-20 Cook Medical Technologies Llc Low profile non-symmetrical stents and stent-grafts
GB2476451A (en) 2009-11-19 2011-06-29 Cook William Europ Stent Graft
US8157852B2 (en) 2008-01-24 2012-04-17 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US9393115B2 (en) 2008-01-24 2016-07-19 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
EP4378420A3 (fr) * 2008-01-24 2024-08-14 Medtronic, Inc. Stents pour valvules cardiaques prothétiques
WO2009094197A1 (fr) 2008-01-24 2009-07-30 Medtronic, Inc. Stents pour valvules cardiaques prothétiques
EP2254512B1 (fr) 2008-01-24 2016-01-06 Medtronic, Inc. Marqueurs pour valvules cardiaques prothétiques
US9149358B2 (en) 2008-01-24 2015-10-06 Medtronic, Inc. Delivery systems for prosthetic heart valves
US7972378B2 (en) 2008-01-24 2011-07-05 Medtronic, Inc. Stents for prosthetic heart valves
WO2009104041A1 (fr) * 2008-02-21 2009-08-27 Valerian Voinov Endoprothèse de valve implantable
GB0803302D0 (en) * 2008-02-22 2008-04-02 Barts & London Nhs Trust Blood vessel prosthesis and delivery apparatus
US9044318B2 (en) 2008-02-26 2015-06-02 Jenavalve Technology Gmbh Stent for the positioning and anchoring of a valvular prosthesis
ES2903231T3 (es) 2008-02-26 2022-03-31 Jenavalve Tech Inc Stent para el posicionamiento y anclaje de una prótesis valvular en un sitio de implantación en el corazón de un paciente
US9168130B2 (en) 2008-02-26 2015-10-27 Jenavalve Technology Gmbh Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
EP2262447B1 (fr) 2008-02-28 2015-08-12 Medtronic, Inc. Systèmes de prothèse de valve cardiaque
DE102008012113A1 (de) 2008-03-02 2009-09-03 Transcatheter Technologies Gmbh Stent, welcher vom expandierten Zustand erneut im Durchmesser kontrolliert verringerbar ist
US8382829B1 (en) 2008-03-10 2013-02-26 Mitralign, Inc. Method to reduce mitral regurgitation by cinching the commissure of the mitral valve
US8313525B2 (en) 2008-03-18 2012-11-20 Medtronic Ventor Technologies, Ltd. Valve suturing and implantation procedures
US8696689B2 (en) * 2008-03-18 2014-04-15 Medtronic Ventor Technologies Ltd. Medical suturing device and method for use thereof
US8430927B2 (en) 2008-04-08 2013-04-30 Medtronic, Inc. Multiple orifice implantable heart valve and methods of implantation
US8696743B2 (en) 2008-04-23 2014-04-15 Medtronic, Inc. Tissue attachment devices and methods for prosthetic heart valves
US8312825B2 (en) 2008-04-23 2012-11-20 Medtronic, Inc. Methods and apparatuses for assembly of a pericardial prosthetic heart valve
US20090276040A1 (en) 2008-05-01 2009-11-05 Edwards Lifesciences Corporation Device and method for replacing mitral valve
ES2386239T3 (es) 2008-05-16 2012-08-14 Sorin Biomedica Cardio S.R.L. Prótesis cardiovalvular atraumática
US8197413B2 (en) * 2008-06-06 2012-06-12 Boston Scientific Scimed, Inc. Transducers, devices and systems containing the transducers, and methods of manufacture
HUE054943T2 (hu) 2008-06-06 2021-10-28 Edwards Lifesciences Corp Kis profilú transzkatéteres szívbillentyû
EP4176845A1 (fr) 2008-07-15 2023-05-10 St. Jude Medical, LLC Conceptions de manchon de valvule cardiaque prothétique repliable et redéployable
ES2421333T3 (es) * 2008-07-17 2013-08-30 Nvt Ag Sistema de prótesis para válvula cardiaca
US8652202B2 (en) 2008-08-22 2014-02-18 Edwards Lifesciences Corporation Prosthetic heart valve and delivery apparatus
WO2010030859A1 (fr) * 2008-09-12 2010-03-18 Valvexchange Inc. Ensemble valvule avec élément valvule échangeable et jeu d'instruments destiné à changer l'élément valvule
WO2010031060A1 (fr) 2008-09-15 2010-03-18 Medtronic Ventor Technologies Ltd. Valvule cardiaque prosthétique ayant des identifiants pour faciliter le positionnement radiographique
US8721714B2 (en) 2008-09-17 2014-05-13 Medtronic Corevalve Llc Delivery system for deployment of medical devices
AU2009295960A1 (en) 2008-09-29 2010-04-01 Cardiaq Valve Technologies, Inc. Heart valve
US8337541B2 (en) * 2008-10-01 2012-12-25 Cardiaq Valve Technologies, Inc. Delivery system for vascular implant
US8790387B2 (en) 2008-10-10 2014-07-29 Edwards Lifesciences Corporation Expandable sheath for introducing an endovascular delivery device into a body
US8137398B2 (en) 2008-10-13 2012-03-20 Medtronic Ventor Technologies Ltd Prosthetic valve having tapered tip when compressed for delivery
WO2010045477A2 (fr) 2008-10-16 2010-04-22 Obalon Therapeutics, Inc. Dispositif occupant un volume intra-gastrique et son procédé de fabrication
US8449625B2 (en) 2009-10-27 2013-05-28 Edwards Lifesciences Corporation Methods of measuring heart valve annuluses for valve replacement
US8986361B2 (en) 2008-10-17 2015-03-24 Medtronic Corevalve, Inc. Delivery system for deployment of medical devices
EP2358297B1 (fr) 2008-11-21 2019-09-11 Percutaneous Cardiovascular Solutions Pty Limited Prothèse de valve cardiaque
WO2010065265A2 (fr) 2008-11-25 2010-06-10 Edwards Lifesciences Corporation Appareil et procédé pour le déploiement in situ d'un dispositif prothétique
US8308798B2 (en) 2008-12-19 2012-11-13 Edwards Lifesciences Corporation Quick-connect prosthetic heart valve and methods
US8241351B2 (en) 2008-12-22 2012-08-14 Valtech Cardio, Ltd. Adjustable partial annuloplasty ring and mechanism therefor
US8715342B2 (en) 2009-05-07 2014-05-06 Valtech Cardio, Ltd. Annuloplasty ring with intra-ring anchoring
US10517719B2 (en) 2008-12-22 2019-12-31 Valtech Cardio, Ltd. Implantation of repair devices in the heart
US8545553B2 (en) 2009-05-04 2013-10-01 Valtech Cardio, Ltd. Over-wire rotation tool
US8926696B2 (en) 2008-12-22 2015-01-06 Valtech Cardio, Ltd. Adjustable annuloplasty devices and adjustment mechanisms therefor
ES2551694T3 (es) 2008-12-23 2015-11-23 Sorin Group Italia S.R.L. Válvula protésica expansible dotada de apéndices de anclaje
US9681950B2 (en) * 2009-01-12 2017-06-20 Valve Medical Ltd. System and method for placing a percutaneous valve device
US8353956B2 (en) 2009-02-17 2013-01-15 Valtech Cardio, Ltd. Actively-engageable movement-restriction mechanism for use with an annuloplasty structure
GB0905444D0 (en) 2009-03-30 2009-05-13 Ucl Business Plc Heart valve prosthesis
US8444689B2 (en) 2009-03-30 2013-05-21 Causper Medical Inc. Valve prosthesis with movably attached claspers with apex
US9980818B2 (en) 2009-03-31 2018-05-29 Edwards Lifesciences Corporation Prosthetic heart valve system with positioning markers
US8414644B2 (en) 2009-04-15 2013-04-09 Cardiaq Valve Technologies, Inc. Vascular implant and delivery system
US8512397B2 (en) 2009-04-27 2013-08-20 Sorin Group Italia S.R.L. Prosthetic vascular conduit
US9968452B2 (en) 2009-05-04 2018-05-15 Valtech Cardio, Ltd. Annuloplasty ring delivery cathethers
US9168105B2 (en) * 2009-05-13 2015-10-27 Sorin Group Italia S.R.L. Device for surgical interventions
EP2250975B1 (fr) * 2009-05-13 2013-02-27 Sorin Biomedica Cardio S.r.l. Dispositif pour la livraison in situ de valvules cardiaques
US8353953B2 (en) * 2009-05-13 2013-01-15 Sorin Biomedica Cardio, S.R.L. Device for the in situ delivery of heart valves
EP2437689B1 (fr) * 2009-06-05 2023-08-02 Medtronic ATS Medical Inc. Structure a commissure flexible servant a fixer une bioprothese de valvule
US8348998B2 (en) 2009-06-26 2013-01-08 Edwards Lifesciences Corporation Unitary quick connect prosthetic heart valve and deployment system and methods
US8439970B2 (en) 2009-07-14 2013-05-14 Edwards Lifesciences Corporation Transapical delivery system for heart valves
US20110077733A1 (en) * 2009-09-25 2011-03-31 Edwards Lifesciences Corporation Leaflet contacting apparatus and method
US8652203B2 (en) 2010-09-23 2014-02-18 Cardiaq Valve Technologies, Inc. Replacement heart valves, delivery devices and methods
US9730790B2 (en) 2009-09-29 2017-08-15 Edwards Lifesciences Cardiaq Llc Replacement valve and method
US8808369B2 (en) 2009-10-05 2014-08-19 Mayo Foundation For Medical Education And Research Minimally invasive aortic valve replacement
US9180007B2 (en) 2009-10-29 2015-11-10 Valtech Cardio, Ltd. Apparatus and method for guide-wire based advancement of an adjustable implant
US10098737B2 (en) 2009-10-29 2018-10-16 Valtech Cardio, Ltd. Tissue anchor for annuloplasty device
WO2011051043A1 (fr) 2009-11-02 2011-05-05 Symetis Sa Bioprothèse aortique et systèmes de mise en place de celle-ci
CN102811672A (zh) * 2009-11-03 2012-12-05 大口径封闭有限责任公司 封闭装置
US9757263B2 (en) 2009-11-18 2017-09-12 Cook Medical Technologies Llc Stent graft and introducer assembly
US9539081B2 (en) 2009-12-02 2017-01-10 Surefire Medical, Inc. Method of operating a microvalve protection device
US8696698B2 (en) * 2009-12-02 2014-04-15 Surefire Medical, Inc. Microvalve protection device and method of use for protection against embolization agent reflux
US8500775B2 (en) * 2009-12-02 2013-08-06 Surefire Medical, Inc. Protection device and method against embolization agent reflux
EP2506777B1 (fr) 2009-12-02 2020-11-25 Valtech Cardio, Ltd. Combinaison d'un ensemble de bobine couplé à un ancrage hélicoïdal et d'un outil distributeur pour son implantation
US8870950B2 (en) 2009-12-08 2014-10-28 Mitral Tech Ltd. Rotation-based anchoring of an implant
US9358109B2 (en) * 2010-01-13 2016-06-07 Vinay Badhwar Transcorporeal delivery system and method
US8475525B2 (en) 2010-01-22 2013-07-02 4Tech Inc. Tricuspid valve repair using tension
US10058323B2 (en) 2010-01-22 2018-08-28 4 Tech Inc. Tricuspid valve repair using tension
US9307980B2 (en) 2010-01-22 2016-04-12 4Tech Inc. Tricuspid valve repair using tension
DE102010008362A1 (de) 2010-02-17 2011-08-18 Transcatheter Technologies GmbH, 93053 Medizinisches Implantat, welches aus einem nicht expandierten Zustand expandierbar ist
US9522062B2 (en) 2010-02-24 2016-12-20 Medtronic Ventor Technologies, Ltd. Mitral prosthesis and methods for implantation
US9226826B2 (en) 2010-02-24 2016-01-05 Medtronic, Inc. Transcatheter valve structure and methods for valve delivery
US8795354B2 (en) 2010-03-05 2014-08-05 Edwards Lifesciences Corporation Low-profile heart valve and delivery system
US20110224785A1 (en) 2010-03-10 2011-09-15 Hacohen Gil Prosthetic mitral valve with tissue anchors
US8992599B2 (en) 2010-03-26 2015-03-31 Thubrikar Aortic Valve, Inc. Valve component, frame component and prosthetic valve device including the same for implantation in a body lumen
US8652204B2 (en) 2010-04-01 2014-02-18 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
US8623075B2 (en) 2010-04-21 2014-01-07 Medtronic, Inc. Transcatheter prosthetic heart valve delivery system and method with controlled expansion of prosthetic heart valve
DK2560580T3 (da) 2010-04-21 2019-08-12 Medtronic Inc Proteseklap med tætningselementer
US8876892B2 (en) 2010-04-21 2014-11-04 Medtronic, Inc. Prosthetic heart valve delivery system with spacing
US8579964B2 (en) 2010-05-05 2013-11-12 Neovasc Inc. Transcatheter mitral valve prosthesis
WO2011143238A2 (fr) 2010-05-10 2011-11-17 Edwards Lifesciences Corporation Valve cardiaque prothétique
CA2798711C (fr) 2010-05-10 2019-08-27 Heart Leaflet Technologies, Inc. Structure de soutien non etayee
US9554901B2 (en) * 2010-05-12 2017-01-31 Edwards Lifesciences Corporation Low gradient prosthetic heart valve
IT1400327B1 (it) 2010-05-21 2013-05-24 Sorin Biomedica Cardio Srl Dispositivo di supporto per protesi valvolari e corrispondente corredo.
JP2013526388A (ja) 2010-05-25 2013-06-24 イエナバルブ テクノロジー インク 人工心臓弁、及び人工心臓弁とステントを備える経カテーテル搬送体内プロテーゼ
EP4018966A1 (fr) 2010-06-21 2022-06-29 Edwards Lifesciences CardiAQ LLC Prothèse de valvule cardiaque
JP5848345B2 (ja) 2010-07-09 2016-01-27 ハイライフ エスエーエス 経カテーテル式房室弁人工器官
US9132009B2 (en) 2010-07-21 2015-09-15 Mitraltech Ltd. Guide wires with commissural anchors to advance a prosthetic valve
US11653910B2 (en) 2010-07-21 2023-05-23 Cardiovalve Ltd. Helical anchor implantation
US9763657B2 (en) 2010-07-21 2017-09-19 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
US8992604B2 (en) 2010-07-21 2015-03-31 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
US9326853B2 (en) * 2010-07-23 2016-05-03 Edwards Lifesciences Corporation Retaining mechanisms for prosthetic valves
US8696737B2 (en) 2010-08-11 2014-04-15 Hlt, Inc. Reinforced commissural support structure
US20120053680A1 (en) 2010-08-24 2012-03-01 Bolling Steven F Reconfiguring Heart Features
JP5970458B2 (ja) * 2010-09-01 2016-08-17 ムバルブ・テクノロジーズ・リミテッド 心臓弁支持構造体
US10105224B2 (en) 2010-09-01 2018-10-23 Mvalve Technologies Ltd. Cardiac valve support structure
AU2011296361B2 (en) * 2010-09-01 2015-05-28 Medtronic Vascular Galway Prosthetic valve support structure
US8641757B2 (en) 2010-09-10 2014-02-04 Edwards Lifesciences Corporation Systems for rapidly deploying surgical heart valves
CN106073946B (zh) * 2010-09-10 2022-01-04 西美蒂斯股份公司 瓣膜置换装置、用于瓣膜置换装置的递送装置以及瓣膜置换装置的生产方法
US9370418B2 (en) 2010-09-10 2016-06-21 Edwards Lifesciences Corporation Rapidly deployable surgical heart valves
US9125741B2 (en) 2010-09-10 2015-09-08 Edwards Lifesciences Corporation Systems and methods for ensuring safe and rapid deployment of prosthetic heart valves
US8845720B2 (en) 2010-09-27 2014-09-30 Edwards Lifesciences Corporation Prosthetic heart valve frame with flexible commissures
US9770319B2 (en) 2010-12-01 2017-09-26 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
US9579197B2 (en) * 2010-12-15 2017-02-28 Medtronic Vascular, Inc. Systems and methods for positioning a heart valve using visual markers
DE102010061371A1 (de) 2010-12-20 2012-06-21 Transcatheter Technologies Gmbh Vorrichtung mit individuellen Schaftfasern und Set zum Falten oder Entfalten eines medizinischen Implantats und Verfahren
JP6010545B2 (ja) 2010-12-23 2016-10-19 トゥエルヴ, インコーポレイテッド 僧帽弁の修復および置換のためのシステム
EP2665512B1 (fr) 2011-01-21 2016-06-29 Obalon Therapeutics, Inc. Dispositif intragastrique
ES2641902T3 (es) 2011-02-14 2017-11-14 Sorin Group Italia S.R.L. Dispositivo de anclaje sin sutura para prótesis valvulares cardiacas
EP2486894B1 (fr) 2011-02-14 2021-06-09 Sorin Group Italia S.r.l. Dispositif d'ancrage sans suture pour prothèses valvulaires cardiaques
US9155619B2 (en) 2011-02-25 2015-10-13 Edwards Lifesciences Corporation Prosthetic heart valve delivery apparatus
EP2688516B1 (fr) 2011-03-21 2022-08-17 Cephea Valve Technologies, Inc. Appareil pour valvule à disques
US9381082B2 (en) 2011-04-22 2016-07-05 Edwards Lifesciences Corporation Devices, systems and methods for accurate positioning of a prosthetic valve
US9554897B2 (en) 2011-04-28 2017-01-31 Neovasc Tiara Inc. Methods and apparatus for engaging a valve prosthesis with tissue
US8840659B2 (en) * 2011-04-28 2014-09-23 Cook Medical Technologies Llc Stent and stent-graft designs
US9308087B2 (en) 2011-04-28 2016-04-12 Neovasc Tiara Inc. Sequentially deployed transcatheter mitral valve prosthesis
EP2520251A1 (fr) 2011-05-05 2012-11-07 Symetis SA Procédé et appareil pour compresser des valvules d'endoprothèse
US8945209B2 (en) 2011-05-20 2015-02-03 Edwards Lifesciences Corporation Encapsulated heart valve
US20120303048A1 (en) 2011-05-24 2012-11-29 Sorin Biomedica Cardio S.R.I. Transapical valve replacement
US8840664B2 (en) * 2011-06-15 2014-09-23 Edwards Lifesciences Corporation Heart valve prosthesis anchoring device and methods
CA2840084C (fr) * 2011-06-21 2019-11-05 Foundry Newco Xii, Inc. Dispositifs de valvule cardiaque prosthetiques et systemes et procedes associes
US9918840B2 (en) 2011-06-23 2018-03-20 Valtech Cardio, Ltd. Closed band for percutaneous annuloplasty
US10792152B2 (en) 2011-06-23 2020-10-06 Valtech Cardio, Ltd. Closed band for percutaneous annuloplasty
WO2013009975A1 (fr) 2011-07-12 2013-01-17 Boston Scientific Scimed, Inc. Système de couplage pour dispositifs médicaux
EP3424468A1 (fr) 2011-07-21 2019-01-09 4Tech Inc. Appareil pour la réparation d'une valvule tricuspide en utilisant une tension
US9339384B2 (en) 2011-07-27 2016-05-17 Edwards Lifesciences Corporation Delivery systems for prosthetic heart valve
US8852272B2 (en) 2011-08-05 2014-10-07 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
US9668859B2 (en) 2011-08-05 2017-06-06 California Institute Of Technology Percutaneous heart valve delivery systems
US20140324164A1 (en) 2011-08-05 2014-10-30 Mitraltech Ltd. Techniques for percutaneous mitral valve replacement and sealing
EP3417813B1 (fr) 2011-08-05 2020-05-13 Cardiovalve Ltd Remplacement percutané d'une valvule mitrale
WO2013021374A2 (fr) 2011-08-05 2013-02-14 Mitraltech Ltd. Techniques pour le remplacement et la fixation percutanés d'une valvule mitrale
US9089668B2 (en) 2011-09-28 2015-07-28 Surefire Medical, Inc. Flow directional infusion device
US9763780B2 (en) 2011-10-19 2017-09-19 Twelve, Inc. Devices, systems and methods for heart valve replacement
WO2013059743A1 (fr) 2011-10-19 2013-04-25 Foundry Newco Xii, Inc. Dispositifs, systèmes et procédés de remplacement de valvule cardiaque
US9655722B2 (en) 2011-10-19 2017-05-23 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
US9039757B2 (en) 2011-10-19 2015-05-26 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
CN107028685B (zh) 2011-10-19 2019-11-15 托尔福公司 人工心脏瓣膜装置、人工二尖瓣和相关系统及方法
US11202704B2 (en) 2011-10-19 2021-12-21 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
US9827093B2 (en) 2011-10-21 2017-11-28 Edwards Lifesciences Cardiaq Llc Actively controllable stent, stent graft, heart valve and method of controlling same
CN104159543B (zh) 2011-10-21 2016-10-12 耶拿阀门科技公司 用于将可扩张心脏瓣膜支架引入患者体内的导管系统
US8858623B2 (en) 2011-11-04 2014-10-14 Valtech Cardio, Ltd. Implant having multiple rotational assemblies
EP2775896B1 (fr) 2011-11-08 2020-01-01 Valtech Cardio, Ltd. Fonction d'orientation commandée d'un outil de pose d'implant
US9131926B2 (en) 2011-11-10 2015-09-15 Boston Scientific Scimed, Inc. Direct connect flush system
US8940014B2 (en) 2011-11-15 2015-01-27 Boston Scientific Scimed, Inc. Bond between components of a medical device
US8951243B2 (en) 2011-12-03 2015-02-10 Boston Scientific Scimed, Inc. Medical device handle
EP2790609B1 (fr) 2011-12-12 2015-09-09 David Alon Dispositif de réparation de valvule cardiaque
US8652145B2 (en) 2011-12-14 2014-02-18 Edwards Lifesciences Corporation System and method for crimping a prosthetic valve
US9510945B2 (en) 2011-12-20 2016-12-06 Boston Scientific Scimed Inc. Medical device handle
US9277993B2 (en) 2011-12-20 2016-03-08 Boston Scientific Scimed, Inc. Medical device delivery systems
US9078747B2 (en) 2011-12-21 2015-07-14 Edwards Lifesciences Corporation Anchoring device for replacing or repairing a heart valve
EP2609893B1 (fr) 2011-12-29 2014-09-03 Sorin Group Italia S.r.l. Kit pour l'implantation de conduits vasculaires prosthétiques
US10172708B2 (en) 2012-01-25 2019-01-08 Boston Scientific Scimed, Inc. Valve assembly with a bioabsorbable gasket and a replaceable valve implant
EP2811939B8 (fr) 2012-02-10 2017-11-15 CVDevices, LLC Produits de tissus biologiques pour endoprothèses vasculaires et procédés de fabrication
CA3097321A1 (fr) 2012-02-22 2013-08-29 Edwards Lifesciences Cardiaq Llc Endoprothese a commande active, greffe d'endoprothese, valve cardiaque et methode de commande de celles-ci
WO2013128432A1 (fr) 2012-02-28 2013-09-06 Mvalve Technologies Ltd. Structure de support de valvule cardiaque
US9089341B2 (en) 2012-02-28 2015-07-28 Surefire Medical, Inc. Renal nerve neuromodulation device
US20130304197A1 (en) * 2012-02-28 2013-11-14 Mvalve Technologies Ltd. Cardiac valve modification device
US9579198B2 (en) 2012-03-01 2017-02-28 Twelve, Inc. Hydraulic delivery systems for prosthetic heart valve devices and associated methods
US20130274873A1 (en) 2012-03-22 2013-10-17 Symetis Sa Transcatheter Stent-Valves and Methods, Systems and Devices for Addressing Para-Valve Leakage
US11207176B2 (en) 2012-03-22 2021-12-28 Boston Scientific Scimed, Inc. Transcatheter stent-valves and methods, systems and devices for addressing para-valve leakage
US9011515B2 (en) 2012-04-19 2015-04-21 Caisson Interventional, LLC Heart valve assembly systems and methods
US9427315B2 (en) 2012-04-19 2016-08-30 Caisson Interventional, LLC Valve replacement systems and methods
WO2013169748A1 (fr) * 2012-05-09 2013-11-14 Boston Scientific Scimed, Inc. Valvule à profil réduit avec éléments de verrouillage
RU2017102580A (ru) * 2012-05-15 2018-12-20 Вэлв Медикал Лтд. Вводимое через кожу модульное клапанное устройство и клапанный модуль для такого устройства
JP6227632B2 (ja) 2012-05-16 2017-11-08 イェーナヴァルヴ テクノロジー ゲゼルシャフト ミット ベシュレンクテル ハフツング 拡張可能心臓代用弁を導入するためのカテーテル送達システムおよび心臓弁欠陥の治療のための医療デバイス
US9345573B2 (en) 2012-05-30 2016-05-24 Neovasc Tiara Inc. Methods and apparatus for loading a prosthesis onto a delivery system
US8961594B2 (en) 2012-05-31 2015-02-24 4Tech Inc. Heart valve repair system
US9883941B2 (en) 2012-06-19 2018-02-06 Boston Scientific Scimed, Inc. Replacement heart valve
US20140005776A1 (en) * 2012-06-29 2014-01-02 St. Jude Medical, Cardiology Division, Inc. Leaflet attachment for function in various shapes and sizes
US20140018902A1 (en) * 2012-07-12 2014-01-16 Makor Issues And Rights Ltd. Tailor-made stent graft and procedure for minimally invasive aneurysm repair with novel tailor-made balloon, novel guidewire, and novel capsulated bioglue
US10206775B2 (en) 2012-08-13 2019-02-19 Medtronic, Inc. Heart valve prosthesis
US9232995B2 (en) 2013-01-08 2016-01-12 Medtronic, Inc. Valve prosthesis and method for delivery
US10849755B2 (en) 2012-09-14 2020-12-01 Boston Scientific Scimed, Inc. Mitral valve inversion prostheses
US10543088B2 (en) 2012-09-14 2020-01-28 Boston Scientific Scimed, Inc. Mitral valve inversion prostheses
US9387080B2 (en) 2012-09-27 2016-07-12 Elwha Llc Artificial joint components including synovial fluid deflecting structures
US8828081B2 (en) 2012-09-27 2014-09-09 Elwha Llc Artificial joint components including synovial fluid deflecting structures
US8845741B2 (en) 2012-09-27 2014-09-30 Seavete LLC Artificial joint components including integral magnetic fields configured to deflect wear debris particles
US8845739B2 (en) 2012-09-27 2014-09-30 Elwha Llc Artificial joint components including mechanized synovial fluid deflecting structures
WO2014052818A1 (fr) 2012-09-29 2014-04-03 Mitralign, Inc. Système de distribution de verrous de plicature et procédé d'utilisation de celui-ci
WO2014064694A2 (fr) 2012-10-23 2014-05-01 Valtech Cardio, Ltd. Fonctionnalité d'orientation commandée pour outil de pose d'implant
WO2014064695A2 (fr) 2012-10-23 2014-05-01 Valtech Cardio, Ltd. Techniques d'ancrage de tissu percutané
US8628571B1 (en) 2012-11-13 2014-01-14 Mitraltech Ltd. Percutaneously-deliverable mechanical valve
US20140155993A1 (en) * 2012-12-04 2014-06-05 The Cleveland Clinic Foundation Device for mitigating or preventing paravalvular leaks
US9730793B2 (en) 2012-12-06 2017-08-15 Valtech Cardio, Ltd. Techniques for guide-wire based advancement of a tool
US9066801B2 (en) 2013-01-08 2015-06-30 Medtronic, Inc. Valve prosthesis and method for delivery
US9788948B2 (en) 2013-01-09 2017-10-17 4 Tech Inc. Soft tissue anchors and implantation techniques
US20140200662A1 (en) * 2013-01-16 2014-07-17 Mvalve Technologies Ltd. Anchoring elements for intracardiac devices
US9681952B2 (en) 2013-01-24 2017-06-20 Mitraltech Ltd. Anchoring of prosthetic valve supports
AU2014214700B2 (en) * 2013-02-11 2018-01-18 Cook Medical Technologies Llc Expandable support frame and medical device
EP2961351B1 (fr) 2013-02-26 2018-11-28 Mitralign, Inc. Dispositif pour réparation percutanée de valve tricuspide
US10583002B2 (en) 2013-03-11 2020-03-10 Neovasc Tiara Inc. Prosthetic valve with anti-pivoting mechanism
US11406497B2 (en) 2013-03-14 2022-08-09 Jc Medical, Inc. Heart valve prosthesis
US9907681B2 (en) 2013-03-14 2018-03-06 4Tech Inc. Stent with tether interface
JP2016512077A (ja) 2013-03-14 2016-04-25 カーディオヴァンテージ・メディカル・インク 塞栓保護デバイスおよび使用方法
ES2824628T3 (es) * 2013-03-14 2021-05-12 Valve Medical Ltd Válvula temporal
US9730791B2 (en) 2013-03-14 2017-08-15 Edwards Lifesciences Cardiaq Llc Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery
US10449333B2 (en) 2013-03-14 2019-10-22 Valtech Cardio, Ltd. Guidewire feeder
US9681951B2 (en) 2013-03-14 2017-06-20 Edwards Lifesciences Cardiaq Llc Prosthesis with outer skirt and anchors
US11259923B2 (en) 2013-03-14 2022-03-01 Jc Medical, Inc. Methods and devices for delivery of a prosthetic valve
US20140277427A1 (en) 2013-03-14 2014-09-18 Cardiaq Valve Technologies, Inc. Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery
CA3060245A1 (fr) 2013-03-15 2014-09-18 Hlt, Inc. Structure de valve prothetique au profil bas
US11007058B2 (en) 2013-03-15 2021-05-18 Edwards Lifesciences Corporation Valved aortic conduits
US10149757B2 (en) 2013-03-15 2018-12-11 Edwards Lifesciences Corporation System and method for transaortic delivery of a prosthetic heart valve
CA2900367C (fr) 2013-03-15 2020-12-22 Edwards Lifesciences Corporation Conduits aortiques a valvule
US9724195B2 (en) 2013-03-15 2017-08-08 Mitralign, Inc. Translation catheters and systems
US9744037B2 (en) 2013-03-15 2017-08-29 California Institute Of Technology Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves
US9572665B2 (en) 2013-04-04 2017-02-21 Neovasc Tiara Inc. Methods and apparatus for delivering a prosthetic valve to a beating heart
US10219724B2 (en) 2013-05-02 2019-03-05 VS Medtech, Inc. Systems and methods for measuring and characterizing interior surfaces of luminal structures
US9629718B2 (en) 2013-05-03 2017-04-25 Medtronic, Inc. Valve delivery tool
ES2908132T3 (es) 2013-05-20 2022-04-27 Edwards Lifesciences Corp Aparato de suministro de válvula cardiaca protésica
EP2999435B1 (fr) 2013-05-20 2022-12-21 Twelve, Inc. Dispositifs de valvule cardiaque pouvant être implantée, dispositifs de réparation de valve mitrale, et systèmes associés
US9468527B2 (en) 2013-06-12 2016-10-18 Edwards Lifesciences Corporation Cardiac implant with integrated suture fasteners
US11076952B2 (en) * 2013-06-14 2021-08-03 The Regents Of The University Of California Collapsible atrioventricular valve prosthesis
US10524904B2 (en) * 2013-07-11 2020-01-07 Medtronic, Inc. Valve positioning device
US9561103B2 (en) 2013-07-17 2017-02-07 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
WO2015013666A1 (fr) 2013-07-26 2015-01-29 Cardiaq Valve Technologies, Inc. Systèmes et procédés pour sceller des ouvertures dans une paroi anatomique
SG10201805117UA (en) 2013-08-12 2018-07-30 Mitral Valve Tech Sarl Apparatus and methods for implanting a replacement heart valve
US9919137B2 (en) 2013-08-28 2018-03-20 Edwards Lifesciences Corporation Integrated balloon catheter inflation system
CN105491978A (zh) 2013-08-30 2016-04-13 耶拿阀门科技股份有限公司 用于假体瓣膜的径向可折叠框架及其制造方法
US10070857B2 (en) 2013-08-31 2018-09-11 Mitralign, Inc. Devices and methods for locating and implanting tissue anchors at mitral valve commissure
US10117742B2 (en) 2013-09-12 2018-11-06 St. Jude Medical, Cardiology Division, Inc. Stent designs for prosthetic heart valves
CA2910602C (fr) 2013-09-20 2020-03-10 Edwards Lifesciences Corporation Valvules cardiaques presentant une zone d'orifice effective augmentee
US9050188B2 (en) 2013-10-23 2015-06-09 Caisson Interventional, LLC Methods and systems for heart valve therapy
US10299793B2 (en) 2013-10-23 2019-05-28 Valtech Cardio, Ltd. Anchor magazine
US9662202B2 (en) 2013-10-24 2017-05-30 Medtronic, Inc. Heart valve prosthesis
US10052095B2 (en) 2013-10-30 2018-08-21 4Tech Inc. Multiple anchoring-point tension system
EP3062709A2 (fr) 2013-10-30 2016-09-07 4Tech Inc. Système de tension à multiples points d'ancrage
US10022114B2 (en) 2013-10-30 2018-07-17 4Tech Inc. Percutaneous tether locking
US20150122687A1 (en) 2013-11-06 2015-05-07 Edwards Lifesciences Corporation Bioprosthetic heart valves having adaptive seals to minimize paravalvular leakage
US9913715B2 (en) 2013-11-06 2018-03-13 St. Jude Medical, Cardiology Division, Inc. Paravalvular leak sealing mechanism
CN111419472B (zh) 2013-11-11 2023-01-10 爱德华兹生命科学卡迪尔克有限责任公司 用于制造支架框架的系统和方法
WO2015077274A1 (fr) 2013-11-19 2015-05-28 St. Jude Medical, Cardiology Division, Inc. Structures d'étanchéité servant de protection contre les fuites paravalvulaires
US10098734B2 (en) 2013-12-05 2018-10-16 Edwards Lifesciences Corporation Prosthetic heart valve and delivery apparatus
US9610162B2 (en) 2013-12-26 2017-04-04 Valtech Cardio, Ltd. Implantation of flexible implant
EP2898920B1 (fr) 2014-01-24 2018-06-06 Cook Medical Technologies LLC Cathéter à ballonnet articulé
US9820852B2 (en) 2014-01-24 2017-11-21 St. Jude Medical, Cardiology Division, Inc. Stationary intra-annular halo designs for paravalvular leak (PVL) reduction—active channel filling cuff designs
US20150209141A1 (en) * 2014-01-24 2015-07-30 St. Jude Medical, Cardiology Division, Inc. Stationary intra-annular halo designs for paravalvular leak (pvl) reduction-passive channel filling cuff designs
CA2910087C (fr) 2014-02-18 2022-06-07 Edwards Lifesciences Corporation Cadre a commissure flexible
CN106170269B (zh) 2014-02-21 2019-01-11 爱德华兹生命科学卡迪尔克有限责任公司 用于瓣膜替代品的受控部署的递送装置
USD755384S1 (en) 2014-03-05 2016-05-03 Edwards Lifesciences Cardiaq Llc Stent
US9889031B1 (en) 2014-03-25 2018-02-13 Surefire Medical, Inc. Method of gastric artery embolization
US9968740B2 (en) 2014-03-25 2018-05-15 Surefire Medical, Inc. Closed tip dynamic microvalve protection device
EP3125826B1 (fr) 2014-03-31 2020-10-07 St. Jude Medical, Cardiology Division, Inc. Étanchéité paravalvulaire via des mécanismes de manchon étendu
US9549816B2 (en) 2014-04-03 2017-01-24 Edwards Lifesciences Corporation Method for manufacturing high durability heart valve
US10154904B2 (en) 2014-04-28 2018-12-18 Edwards Lifesciences Corporation Intravascular introducer devices
US9585752B2 (en) 2014-04-30 2017-03-07 Edwards Lifesciences Corporation Holder and deployment system for surgical heart valves
WO2015171743A2 (fr) 2014-05-07 2015-11-12 Baylor College Of Medicine Valves flexibles artificielles et procédés de fabrication et expansion en série de celles-ci
US10195025B2 (en) 2014-05-12 2019-02-05 Edwards Lifesciences Corporation Prosthetic heart valve
US20150328000A1 (en) 2014-05-19 2015-11-19 Cardiaq Valve Technologies, Inc. Replacement mitral valve with annular flap
EP3134033B1 (fr) 2014-05-29 2018-04-04 Edwards Lifesciences CardiAQ LLC Prothèse et dispositif de mise en place
US9532870B2 (en) 2014-06-06 2017-01-03 Edwards Lifesciences Corporation Prosthetic valve for replacing a mitral valve
US9974647B2 (en) 2014-06-12 2018-05-22 Caisson Interventional, LLC Two stage anchor and mitral valve assembly
JP6559161B2 (ja) 2014-06-19 2019-08-14 4テック インコーポレイテッド 心臓組織の緊締
USD867594S1 (en) 2015-06-19 2019-11-19 Edwards Lifesciences Corporation Prosthetic heart valve
CA2914094C (fr) 2014-06-20 2021-01-05 Edwards Lifesciences Corporation Valvules cardiaques identifiables apres la mise en place
CN107106190B (zh) 2014-07-08 2020-02-28 阿维格公司 高速慢性全闭塞部横穿装置
US9180005B1 (en) 2014-07-17 2015-11-10 Millipede, Inc. Adjustable endolumenal mitral valve ring
US10524910B2 (en) 2014-07-30 2020-01-07 Mitraltech Ltd. 3 Ariel Sharon Avenue Articulatable prosthetic valve
US10016272B2 (en) 2014-09-12 2018-07-10 Mitral Valve Technologies Sarl Mitral repair and replacement devices and methods
US20160095701A1 (en) * 2014-10-07 2016-04-07 St. Jude Medical, Cardiology Division, Inc. Bi-Leaflet Mitral Valve Design
EP4331503A3 (fr) 2014-10-14 2024-06-05 Edwards Lifesciences Innovation (Israel) Ltd. Techniques de restriction de feuillet
US9750605B2 (en) 2014-10-23 2017-09-05 Caisson Interventional, LLC Systems and methods for heart valve therapy
US9750607B2 (en) 2014-10-23 2017-09-05 Caisson Interventional, LLC Systems and methods for heart valve therapy
US9901445B2 (en) 2014-11-21 2018-02-27 Boston Scientific Scimed, Inc. Valve locking mechanism
US9907547B2 (en) 2014-12-02 2018-03-06 4Tech Inc. Off-center tissue anchors
US9492273B2 (en) 2014-12-09 2016-11-15 Cephea Valve Technologies, Inc. Replacement cardiac valves and methods of use and manufacture
EP3037064B1 (fr) 2014-12-23 2018-03-14 Venus MedTech (HangZhou), Inc. Remplacement de valvule mitrale à invasion minimale avec bord
WO2016115375A1 (fr) 2015-01-16 2016-07-21 Boston Scientific Scimed, Inc. Mécanisme de libération et de verrouillage en fonction d'un déplacement
US9861477B2 (en) 2015-01-26 2018-01-09 Boston Scientific Scimed Inc. Prosthetic heart valve square leaflet-leaflet stitch
US9788942B2 (en) 2015-02-03 2017-10-17 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
US10201417B2 (en) 2015-02-03 2019-02-12 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
CA3162308A1 (fr) 2015-02-05 2016-08-11 Cardiovalve Ltd. Valvule prosthetique a chassis coulissants sur le plan axial
US9974651B2 (en) 2015-02-05 2018-05-22 Mitral Tech Ltd. Prosthetic valve with axially-sliding frames
WO2016130991A1 (fr) 2015-02-13 2016-08-18 Millipede, Inc. Remplacement de valvule à l'aide d'ancrages rotatifs
US20160256269A1 (en) 2015-03-05 2016-09-08 Mitralign, Inc. Devices for treating paravalvular leakage and methods use thereof
US10426617B2 (en) 2015-03-06 2019-10-01 Boston Scientific Scimed, Inc. Low profile valve locking mechanism and commissure assembly
US10285809B2 (en) 2015-03-06 2019-05-14 Boston Scientific Scimed Inc. TAVI anchoring assist device
US10080652B2 (en) 2015-03-13 2018-09-25 Boston Scientific Scimed, Inc. Prosthetic heart valve having an improved tubular seal
CN107613908B (zh) 2015-03-19 2020-03-10 凯森因特万逊奈尔有限公司 用于心脏瓣膜疗法的系统和方法
US20160287839A1 (en) 2015-03-31 2016-10-06 Surefire Medical, Inc. Apparatus and Method for Infusing an Immunotherapy Agent to a Solid Tumor for Treatment
US10792471B2 (en) 2015-04-10 2020-10-06 Edwards Lifesciences Corporation Expandable sheath
US10327896B2 (en) 2015-04-10 2019-06-25 Edwards Lifesciences Corporation Expandable sheath with elastomeric cross sectional portions
US10441416B2 (en) 2015-04-21 2019-10-15 Edwards Lifesciences Corporation Percutaneous mitral valve replacement device
KR101588310B1 (ko) * 2015-04-22 2016-01-25 (주)태웅메디칼 심낭막을 이용한 인공심장판막 및 그 제조방법
SG10202010021SA (en) 2015-04-30 2020-11-27 Valtech Cardio Ltd Annuloplasty technologies
US10376363B2 (en) 2015-04-30 2019-08-13 Edwards Lifesciences Cardiaq Llc Replacement mitral valve, delivery system for replacement mitral valve and methods of use
WO2016177562A1 (fr) 2015-05-01 2016-11-10 Jenavalve Technology, Inc. Dispositif et procédé à débit réduit de stimulateur cardiaque lors d'un remplacement de valvules cardiaques
US10849746B2 (en) 2015-05-14 2020-12-01 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
AU2016262564B2 (en) 2015-05-14 2020-11-05 Cephea Valve Technologies, Inc. Replacement mitral valves
US10016273B2 (en) 2015-06-05 2018-07-10 Medtronic, Inc. Filtered sealing components for a transcatheter valve prosthesis
US10226335B2 (en) 2015-06-22 2019-03-12 Edwards Lifesciences Cardiaq Llc Actively controllable heart valve implant and method of controlling same
US10092400B2 (en) 2015-06-23 2018-10-09 Edwards Lifesciences Cardiaq Llc Systems and methods for anchoring and sealing a prosthetic heart valve
CA2989437C (fr) 2015-07-02 2023-08-08 Edwards Lifesciences Corporation Valvules cardiaques hybrides adaptees a dilatation post-implantation
CR20170597A (es) 2015-07-02 2018-04-20 Edwards Lifesciences Corp Válvulas cardíacas hibridas integradas
US10335277B2 (en) 2015-07-02 2019-07-02 Boston Scientific Scimed Inc. Adjustable nosecone
US10195392B2 (en) 2015-07-02 2019-02-05 Boston Scientific Scimed, Inc. Clip-on catheter
US9974650B2 (en) 2015-07-14 2018-05-22 Edwards Lifesciences Corporation Prosthetic heart valve
US10179041B2 (en) 2015-08-12 2019-01-15 Boston Scientific Scimed Icn. Pinless release mechanism
US10136991B2 (en) 2015-08-12 2018-11-27 Boston Scientific Scimed Inc. Replacement heart valve implant
CN111658234B (zh) 2015-08-21 2023-03-10 托尔福公司 可植入心脏瓣膜装置、二尖瓣修复装置以及相关系统和方法
US10117744B2 (en) 2015-08-26 2018-11-06 Edwards Lifesciences Cardiaq Llc Replacement heart valves and methods of delivery
US10575951B2 (en) 2015-08-26 2020-03-03 Edwards Lifesciences Cardiaq Llc Delivery device and methods of use for transapical delivery of replacement mitral valve
US10350066B2 (en) 2015-08-28 2019-07-16 Edwards Lifesciences Cardiaq Llc Steerable delivery system for replacement mitral valve and methods of use
CA2995855C (fr) 2015-09-02 2024-01-30 Edwards Lifesciences Corporation Espaceur pour fixer une valve transcatheter a une structure cardiaque bioprothetique
US10350047B2 (en) 2015-09-02 2019-07-16 Edwards Lifesciences Corporation Method and system for packaging and preparing a prosthetic heart valve and associated delivery system
US10779940B2 (en) 2015-09-03 2020-09-22 Boston Scientific Scimed, Inc. Medical device handle
US10080653B2 (en) 2015-09-10 2018-09-25 Edwards Lifesciences Corporation Limited expansion heart valve
US10314703B2 (en) 2015-09-21 2019-06-11 Edwards Lifesciences Corporation Cylindrical implant and balloon
US10335275B2 (en) 2015-09-29 2019-07-02 Millipede, Inc. Methods for delivery of heart valve devices using intravascular ultrasound imaging
CN108992209B (zh) * 2015-11-06 2022-03-04 麦克尔有限公司 二尖瓣假体
US10321996B2 (en) 2015-11-11 2019-06-18 Edwards Lifesciences Corporation Prosthetic valve delivery apparatus having clutch mechanism
JP6892446B2 (ja) 2015-11-17 2021-06-23 ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. 心臓弁輪を再成形するインプラント可能な機器および送達システム
US10265169B2 (en) 2015-11-23 2019-04-23 Edwards Lifesciences Corporation Apparatus for controlled heart valve delivery
US11033387B2 (en) 2015-11-23 2021-06-15 Edwards Lifesciences Corporation Methods for controlled heart valve delivery
US10357351B2 (en) 2015-12-04 2019-07-23 Edwards Lifesciences Corporation Storage assembly for prosthetic valve
US9931204B2 (en) 2015-12-10 2018-04-03 Medtronic, Inc. Transcatheter heart valve replacement systems, heart valve prostheses, and methods for percutaneous heart valve replacement
JP7002451B2 (ja) 2015-12-15 2022-01-20 ニオバスク ティアラ インコーポレイテッド 経中隔送達システム
US10537453B2 (en) 2015-12-16 2020-01-21 Obalon Therapeutics, Inc. Intragastric device with expandable portions
US10265166B2 (en) 2015-12-30 2019-04-23 Caisson Interventional, LLC Systems and methods for heart valve therapy
US10751182B2 (en) 2015-12-30 2020-08-25 Edwards Lifesciences Corporation System and method for reshaping right heart
WO2017117370A2 (fr) 2015-12-30 2017-07-06 Mitralign, Inc. Système et procédé de réduction de régurgitation tricuspide
WO2017127939A1 (fr) 2016-01-29 2017-08-03 Neovasc Tiara Inc. Valvule prothétique permettant d'éviter une obstruction empêchant l'écoulement
US10342660B2 (en) 2016-02-02 2019-07-09 Boston Scientific Inc. Tensioned sheathing aids
US10363130B2 (en) 2016-02-05 2019-07-30 Edwards Lifesciences Corporation Devices and systems for docking a heart valve
US10179043B2 (en) 2016-02-12 2019-01-15 Edwards Lifesciences Corporation Prosthetic heart valve having multi-level sealing member
US10531866B2 (en) 2016-02-16 2020-01-14 Cardiovalve Ltd. Techniques for providing a replacement valve and transseptal communication
US10667904B2 (en) 2016-03-08 2020-06-02 Edwards Lifesciences Corporation Valve implant with integrated sensor and transmitter
US10888420B2 (en) 2016-03-14 2021-01-12 Medtronic Vascular, Inc. Stented prosthetic heart valve having a wrap and delivery devices
US10398549B2 (en) 2016-03-15 2019-09-03 Abbott Cardiovascular Systems Inc. System and method for transcatheter heart valve platform
CR20180410A (es) 2016-03-24 2019-04-01 Edwards Lifesciences Corp Sistema de entrega de válvula cardíaca protésica
USD815744S1 (en) 2016-04-28 2018-04-17 Edwards Lifesciences Cardiaq Llc Valve frame for a delivery system
CN109069272A (zh) 2016-04-29 2018-12-21 美敦力瓦斯科尔勒公司 具有带系绳的锚定件的假体心脏瓣膜设备以及相关联的系统和方法
US10583005B2 (en) 2016-05-13 2020-03-10 Boston Scientific Scimed, Inc. Medical device handle
US10245136B2 (en) 2016-05-13 2019-04-02 Boston Scientific Scimed Inc. Containment vessel with implant sheathing guide
JP7081749B2 (ja) 2016-05-13 2022-06-07 イエナバルブ テクノロジー インク 心臓弁プロテーゼ送達システム
US10201416B2 (en) 2016-05-16 2019-02-12 Boston Scientific Scimed, Inc. Replacement heart valve implant with invertible leaflets
US10456245B2 (en) 2016-05-16 2019-10-29 Edwards Lifesciences Corporation System and method for applying material to a stent
US10702274B2 (en) 2016-05-26 2020-07-07 Edwards Lifesciences Corporation Method and system for closing left atrial appendage
US11331187B2 (en) 2016-06-17 2022-05-17 Cephea Valve Technologies, Inc. Cardiac valve delivery devices and systems
GB201611910D0 (en) 2016-07-08 2016-08-24 Valtech Cardio Ltd Adjustable annuloplasty device with alternating peaks and troughs
US10350062B2 (en) 2016-07-21 2019-07-16 Edwards Lifesciences Corporation Replacement heart valve prosthesis
GB201613219D0 (en) 2016-08-01 2016-09-14 Mitraltech Ltd Minimally-invasive delivery systems
US11096781B2 (en) 2016-08-01 2021-08-24 Edwards Lifesciences Corporation Prosthetic heart valve
EP3848003A1 (fr) 2016-08-10 2021-07-14 Cardiovalve Ltd. Valve prothétique avec cadres concentriques
USD800908S1 (en) 2016-08-10 2017-10-24 Mitraltech Ltd. Prosthetic valve element
US10383725B2 (en) 2016-08-11 2019-08-20 4C Medical Technologies, Inc. Heart chamber prosthetic valve implant with base, mesh and dome sections with single chamber anchoring for preservation, supplementation and/or replacement of native valve function
EP3500214A4 (fr) 2016-08-19 2019-07-24 Edwards Lifesciences Corporation Système de pose maniable pour valvule mitrale de remplacement et procédés d'utilisation
EP3503848B1 (fr) 2016-08-26 2021-09-22 Edwards Lifesciences Corporation Prothèse de valve cardiaque de remplacement à parties multiples
US10780250B1 (en) 2016-09-19 2020-09-22 Surefire Medical, Inc. System and method for selective pressure-controlled therapeutic delivery
US11400263B1 (en) 2016-09-19 2022-08-02 Trisalus Life Sciences, Inc. System and method for selective pressure-controlled therapeutic delivery
US10575944B2 (en) 2016-09-22 2020-03-03 Edwards Lifesciences Corporation Prosthetic heart valve with reduced stitching
US10729542B2 (en) * 2016-10-26 2020-08-04 Medtronic Vascular, Inc. Stented prosthetic heart valve having a paravalvular sealing wrap
US10758348B2 (en) 2016-11-02 2020-09-01 Edwards Lifesciences Corporation Supra and sub-annular mitral valve delivery system
US10973631B2 (en) 2016-11-17 2021-04-13 Edwards Lifesciences Corporation Crimping accessory device for a prosthetic valve
US10463484B2 (en) 2016-11-17 2019-11-05 Edwards Lifesciences Corporation Prosthetic heart valve having leaflet inflow below frame
CN113893064A (zh) 2016-11-21 2022-01-07 内奥瓦斯克迪亚拉公司 用于快速收回经导管心脏瓣膜递送系统的方法和系统
US10603165B2 (en) 2016-12-06 2020-03-31 Edwards Lifesciences Corporation Mechanically expanding heart valve and delivery apparatus therefor
USD846122S1 (en) 2016-12-16 2019-04-16 Edwards Lifesciences Corporation Heart valve sizer
US10813749B2 (en) 2016-12-20 2020-10-27 Edwards Lifesciences Corporation Docking device made with 3D woven fabric
US10653523B2 (en) 2017-01-19 2020-05-19 4C Medical Technologies, Inc. Systems, methods and devices for delivery systems, methods and devices for implanting prosthetic heart valves
US10433993B2 (en) 2017-01-20 2019-10-08 Medtronic Vascular, Inc. Valve prosthesis having a radially-expandable sleeve integrated thereon for delivery and prevention of paravalvular leakage
US11013600B2 (en) 2017-01-23 2021-05-25 Edwards Lifesciences Corporation Covered prosthetic heart valve
CR20190381A (es) 2017-01-23 2019-09-27 Cephea Valve Tech Inc Valvulas mitrales de reemplazo
US11654023B2 (en) 2017-01-23 2023-05-23 Edwards Lifesciences Corporation Covered prosthetic heart valve
EP4209196A1 (fr) 2017-01-23 2023-07-12 Cephea Valve Technologies, Inc. Valvules mitrales de remplacement
US11185406B2 (en) 2017-01-23 2021-11-30 Edwards Lifesciences Corporation Covered prosthetic heart valve
US10561495B2 (en) 2017-01-24 2020-02-18 4C Medical Technologies, Inc. Systems, methods and devices for two-step delivery and implantation of prosthetic heart valve
CN110392557A (zh) 2017-01-27 2019-10-29 耶拿阀门科技股份有限公司 心脏瓣膜模拟
USD867595S1 (en) 2017-02-01 2019-11-19 Edwards Lifesciences Corporation Stent
CN110381887B (zh) 2017-02-10 2022-03-29 波士顿科学国际有限公司 用于重塑心脏瓣膜环的可植入装置和输送系统
US12029647B2 (en) 2017-03-07 2024-07-09 4C Medical Technologies, Inc. Systems, methods and devices for prosthetic heart valve with single valve leaflet
US10588636B2 (en) 2017-03-20 2020-03-17 Surefire Medical, Inc. Dynamic reconfigurable microvalve protection device
US10463485B2 (en) 2017-04-06 2019-11-05 Edwards Lifesciences Corporation Prosthetic valve holders with automatic deploying mechanisms
US10575950B2 (en) 2017-04-18 2020-03-03 Twelve, Inc. Hydraulic systems for delivering prosthetic heart valve devices and associated methods
US11045627B2 (en) 2017-04-18 2021-06-29 Edwards Lifesciences Corporation Catheter system with linear actuation control mechanism
US10702378B2 (en) 2017-04-18 2020-07-07 Twelve, Inc. Prosthetic heart valve device and associated systems and methods
US10433961B2 (en) 2017-04-18 2019-10-08 Twelve, Inc. Delivery systems with tethers for prosthetic heart valve devices and associated methods
EP3614969B1 (fr) 2017-04-28 2023-05-03 Edwards Lifesciences Corporation Valvule cardiaque prothétique avec support pliable
US10959846B2 (en) 2017-05-10 2021-03-30 Edwards Lifesciences Corporation Mitral valve spacer device
US10792151B2 (en) 2017-05-11 2020-10-06 Twelve, Inc. Delivery systems for delivering prosthetic heart valve devices and associated methods
US10842619B2 (en) 2017-05-12 2020-11-24 Edwards Lifesciences Corporation Prosthetic heart valve docking assembly
US11135056B2 (en) 2017-05-15 2021-10-05 Edwards Lifesciences Corporation Devices and methods of commissure formation for prosthetic heart valve
EP4427706A2 (fr) 2017-05-22 2024-09-11 Edwards Lifesciences Corporation Ancrage de soupape et procédé d'installation
US12064341B2 (en) 2017-05-31 2024-08-20 Edwards Lifesciences Corporation Sealing member for prosthetic heart valve
US10646338B2 (en) 2017-06-02 2020-05-12 Twelve, Inc. Delivery systems with telescoping capsules for deploying prosthetic heart valve devices and associated methods
US10869759B2 (en) 2017-06-05 2020-12-22 Edwards Lifesciences Corporation Mechanically expandable heart valve
US11026785B2 (en) 2017-06-05 2021-06-08 Edwards Lifesciences Corporation Mechanically expandable heart valve
US10709591B2 (en) 2017-06-06 2020-07-14 Twelve, Inc. Crimping device and method for loading stents and prosthetic heart valves
US10828154B2 (en) 2017-06-08 2020-11-10 Boston Scientific Scimed, Inc. Heart valve implant commissure support structure
US12036113B2 (en) 2017-06-14 2024-07-16 4C Medical Technologies, Inc. Delivery of heart chamber prosthetic valve implant
WO2018237020A1 (fr) 2017-06-21 2018-12-27 Edwards Lifesciences Corporation Valvules cardiaques à expansion limitée en forme de double fil
CN111050668A (zh) * 2017-07-06 2020-04-21 拉古维尔·巴苏德 组织抓取装置及相关方法
US11123186B2 (en) 2017-07-06 2021-09-21 Edwards Lifesciences Corporation Steerable delivery system and components
US10786352B2 (en) 2017-07-06 2020-09-29 Twelve, Inc. Prosthetic heart valve devices and associated systems and methods
US10729541B2 (en) 2017-07-06 2020-08-04 Twelve, Inc. Prosthetic heart valve devices and associated systems and methods
US10918473B2 (en) 2017-07-18 2021-02-16 Edwards Lifesciences Corporation Transcatheter heart valve storage container and crimping mechanism
CN111163729B (zh) 2017-08-01 2022-03-29 波士顿科学国际有限公司 医疗植入物锁定机构
US10575948B2 (en) 2017-08-03 2020-03-03 Cardiovalve Ltd. Prosthetic heart valve
US11793633B2 (en) 2017-08-03 2023-10-24 Cardiovalve Ltd. Prosthetic heart valve
US11246704B2 (en) 2017-08-03 2022-02-15 Cardiovalve Ltd. Prosthetic heart valve
US10537426B2 (en) 2017-08-03 2020-01-21 Cardiovalve Ltd. Prosthetic heart valve
US12064347B2 (en) 2017-08-03 2024-08-20 Cardiovalve Ltd. Prosthetic heart valve
US10888421B2 (en) 2017-09-19 2021-01-12 Cardiovalve Ltd. Prosthetic heart valve with pouch
EP3664749B1 (fr) 2017-08-11 2023-07-26 Edwards Lifesciences Corporation Élément d'étanchéité pour valvule cardiaque prothétique
US11083575B2 (en) 2017-08-14 2021-08-10 Edwards Lifesciences Corporation Heart valve frame design with non-uniform struts
US10932903B2 (en) 2017-08-15 2021-03-02 Edwards Lifesciences Corporation Skirt assembly for implantable prosthetic valve
CN111225633B (zh) 2017-08-16 2022-05-31 波士顿科学国际有限公司 置换心脏瓣膜接合组件
US10898319B2 (en) 2017-08-17 2021-01-26 Edwards Lifesciences Corporation Sealing member for prosthetic heart valve
US10973628B2 (en) 2017-08-18 2021-04-13 Edwards Lifesciences Corporation Pericardial sealing member for prosthetic heart valve
US10722353B2 (en) 2017-08-21 2020-07-28 Edwards Lifesciences Corporation Sealing member for prosthetic heart valve
US10856984B2 (en) 2017-08-25 2020-12-08 Neovasc Tiara Inc. Sequentially deployed transcatheter mitral valve prosthesis
US10973629B2 (en) 2017-09-06 2021-04-13 Edwards Lifesciences Corporation Sealing member for prosthetic heart valve
US11147667B2 (en) 2017-09-08 2021-10-19 Edwards Lifesciences Corporation Sealing member for prosthetic heart valve
US11337803B2 (en) 2017-09-19 2022-05-24 Cardiovalve Ltd. Prosthetic valve with inner and outer frames connected at a location of tissue anchor portion
US10835221B2 (en) 2017-11-02 2020-11-17 Valtech Cardio, Ltd. Implant-cinching devices and systems
KR102658756B1 (ko) * 2017-11-16 2024-04-19 칠드런'즈 메디컬 센터 코포레이션 기하학적 수용 심장 판막 치환 디바이스
US11135062B2 (en) 2017-11-20 2021-10-05 Valtech Cardio Ltd. Cinching of dilated heart muscle
GB201720803D0 (en) 2017-12-13 2018-01-24 Mitraltech Ltd Prosthetic Valve and delivery tool therefor
CN210673509U (zh) 2018-01-07 2020-06-05 苏州杰成医疗科技有限公司 瓣膜假体递送装置
JP6990315B2 (ja) 2018-01-07 2022-01-12 ジェイシー メディカル、インコーポレイテッド 人工心臓弁送達システム
GB201800399D0 (en) 2018-01-10 2018-02-21 Mitraltech Ltd Temperature-control during crimping of an implant
EP3740160A2 (fr) 2018-01-19 2020-11-25 Boston Scientific Scimed Inc. Capteurs de déploiement de mode d'inductance de système de valve transcathéter
US11246625B2 (en) 2018-01-19 2022-02-15 Boston Scientific Scimed, Inc. Medical device delivery system with feedback loop
WO2019144121A1 (fr) 2018-01-22 2019-07-25 Edwards Lifesciences Corporation Ancre de préservation de la forme du cœur
WO2019147497A1 (fr) 2018-01-23 2019-08-01 Edwards Lifesciences Corporation Supports de valvule prothétiques, systèmes et procédés
CA3086884A1 (fr) 2018-01-24 2019-08-01 Valtech Cardio, Ltd. Contraction d'une structure d'annuloplastie
WO2019147846A2 (fr) 2018-01-25 2019-08-01 Edwards Lifesciences Corporation Système de distribution pour recapture de valvule de remplacement assistée et post-déploiement de repositionnement
WO2019145941A1 (fr) 2018-01-26 2019-08-01 Valtech Cardio, Ltd. Techniques pour faciliter la fixation de valve cardiaque et le remplacement de cordon
WO2019157156A1 (fr) 2018-02-07 2019-08-15 Boston Scientific Scimed, Inc. Système de pose de dispositif médical avec élément d'alignement
EP3758651B1 (fr) 2018-02-26 2022-12-07 Boston Scientific Scimed, Inc. Marqueur radio-opaque intégré dans un joint adaptatif
US11051934B2 (en) 2018-02-28 2021-07-06 Edwards Lifesciences Corporation Prosthetic mitral valve with improved anchors and seal
US20210068951A1 (en) * 2018-03-21 2021-03-11 Cornell University Mitral valves with integrated cutting features
US11318011B2 (en) 2018-04-27 2022-05-03 Edwards Lifesciences Corporation Mechanically expandable heart valve with leaflet clamps
KR20210003220A (ko) * 2018-04-30 2021-01-11 에드워즈 라이프사이언시스 코포레이션 개선된 시스 패턴
GB2574576B (en) * 2018-05-01 2022-07-20 The David J Wheatley Discretionary Trust Heart valve
US11229517B2 (en) 2018-05-15 2022-01-25 Boston Scientific Scimed, Inc. Replacement heart valve commissure assembly
CA3101165A1 (fr) 2018-05-23 2019-11-28 Sorin Group Italia S.R.L. Prothese de valvule cardiaque
WO2019241477A1 (fr) 2018-06-13 2019-12-19 Boston Scientific Scimed, Inc. Dispositif de pose de valvule cardiaque de remplacement
USD908874S1 (en) 2018-07-11 2021-01-26 Edwards Lifesciences Corporation Collapsible heart valve sizer
MX2020013973A (es) 2018-07-12 2021-06-15 Valtech Cardio Ltd Sistemas de anuloplastia y herramientas de bloqueo para ello.
US11850398B2 (en) 2018-08-01 2023-12-26 Trisalus Life Sciences, Inc. Systems and methods for pressure-facilitated therapeutic agent delivery
US11857441B2 (en) 2018-09-04 2024-01-02 4C Medical Technologies, Inc. Stent loading device
US11338117B2 (en) 2018-10-08 2022-05-24 Trisalus Life Sciences, Inc. Implantable dual pathway therapeutic agent delivery port
CN112867468B (zh) 2018-10-19 2024-08-23 爱德华兹生命科学公司 具有非圆柱形框架的假体心脏瓣膜
CN113271890B (zh) 2018-11-08 2024-08-30 内奥瓦斯克迪亚拉公司 经导管二尖瓣假体的心室展开
CN109350307B (zh) * 2018-12-03 2023-08-29 宁波健世科技股份有限公司 一种经导管人工瓣膜置换系统
WO2020123486A1 (fr) 2018-12-10 2020-06-18 Boston Scientific Scimed, Inc. Système d'administration de dispositif médical comprenant un élément de résistance
JP2022517423A (ja) 2019-01-17 2022-03-08 エドワーズ ライフサイエンシーズ コーポレイション 人工弁用のフレーム
AU2020233892A1 (en) 2019-03-08 2021-11-04 Neovasc Tiara Inc. Retrievable prosthesis delivery system
WO2020198273A2 (fr) 2019-03-26 2020-10-01 Edwards Lifesciences Corporation Prothèse valvulaire cardiaque
WO2020206012A1 (fr) 2019-04-01 2020-10-08 Neovasc Tiara Inc. Valve prothétique déployable de manière contrôlable
WO2020210652A1 (fr) 2019-04-10 2020-10-15 Neovasc Tiara Inc. Valvule prothétique à circulation sanguine naturelle
US11439504B2 (en) 2019-05-10 2022-09-13 Boston Scientific Scimed, Inc. Replacement heart valve with improved cusp washout and reduced loading
CN114025813B (zh) 2019-05-20 2024-05-14 内奥瓦斯克迪亚拉公司 具有止血机构的引入器
WO2020257643A1 (fr) 2019-06-20 2020-12-24 Neovasc Tiara Inc. Valve mitrale prothétique à profil bas
AU2020375903A1 (en) 2019-10-29 2021-12-23 Edwards Lifesciences Innovation (Israel) Ltd. Annuloplasty and tissue anchor technologies
WO2021126778A1 (fr) 2019-12-16 2021-06-24 Edwards Lifesciences Corporation Ensemble porte-valvule avec protection de boucle de suture
US11801131B2 (en) 2019-12-20 2023-10-31 Medtronic Vascular, Inc. Elliptical heart valve prostheses, delivery systems, and methods of use
US11931253B2 (en) 2020-01-31 2024-03-19 4C Medical Technologies, Inc. Prosthetic heart valve delivery system: ball-slide attachment
US12053375B2 (en) 2020-03-05 2024-08-06 4C Medical Technologies, Inc. Prosthetic mitral valve with improved atrial and/or annular apposition and paravalvular leakage mitigation
US11992403B2 (en) 2020-03-06 2024-05-28 4C Medical Technologies, Inc. Devices, systems and methods for improving recapture of prosthetic heart valve device with stent frame having valve support with inwardly stent cells
US12023247B2 (en) 2020-05-20 2024-07-02 Edwards Lifesciences Corporation Reducing the diameter of a cardiac valve annulus with independent control over each of the anchors that are launched into the annulus
EP4167911A1 (fr) 2020-06-18 2023-04-26 Edwards Lifesciences Corporation Procédés de sertissage
CN111772882B (zh) * 2020-08-17 2021-07-13 四川大学 一种便于控制的肺动脉支架以及肺动脉瓣膜置换装置
EP4243736A1 (fr) 2020-11-10 2023-09-20 Edwards Lifesciences Corporation Valvules cardiaques prothétiques dotées de couches hermétiques ou de structures valvulaires pour réduire le risque de thrombose
CN114681126A (zh) * 2020-12-28 2022-07-01 杭州德晋医疗科技有限公司 多支架的瓣膜扩张器及瓣膜扩张系统
KR20230132822A (ko) 2021-01-20 2023-09-18 에드워즈 라이프사이언시스 코포레이션 판막엽을 인공 심장 판막의 프레임에 부착하기 위한연결 스커트
EP4312883A1 (fr) 2021-03-23 2024-02-07 Edwards Lifesciences Corporation Valvule prothétique cardiaque présentant un élément d'étanchéité allongé
WO2023161766A1 (fr) * 2022-02-25 2023-08-31 Medtronic, Inc. Prothèse valvulaire cardiaque
US11969342B2 (en) 2022-08-03 2024-04-30 The Children's Medical Center Corporation Geometrically-accommodating heart valve replacement device
US20240164895A1 (en) * 2022-11-21 2024-05-23 St. Jude Medical, Cardiology Division, Inc. Transcatheter Prosthetic Atrioventricular Valve with Stiffening Structure

Citations (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4768523A (en) 1981-04-29 1988-09-06 Lifecore Biomedical, Inc. Hydrogel adhesive
US5055046A (en) 1990-09-20 1991-10-08 Isp Investments Inc. Bioadhesive composition
US5066709A (en) 1990-09-20 1991-11-19 Gaf Chemicals Corporation Bioadhesive composition
US5156911A (en) 1989-05-11 1992-10-20 Landec Labs Inc. Skin-activated temperature-sensitive adhesive assemblies
US5197973A (en) 1990-12-14 1993-03-30 Creative Biomolecules, Inc. Synthetic bioadhesive
US5225196A (en) 1983-11-14 1993-07-06 Columbia Laboratories, Inc. Bioadhesive compositions and methods of treatment therewith
US5387450A (en) 1989-05-11 1995-02-07 Landec Corporation Temperature-activated adhesive assemblies
US5407671A (en) 1986-07-05 1995-04-18 Behringwerke Aktiengesellschaft One-component tissue adhesive and a process for the production thereof
US5549904A (en) 1993-06-03 1996-08-27 Orthogene, Inc. Biological adhesive composition and method of promoting adhesion between tissue surfaces
US5578310A (en) 1992-04-23 1996-11-26 Berlex Laboratories Inc. Topical bioadhesive ointment compositions and their use in wound healing
US5645062A (en) 1993-02-15 1997-07-08 Anderson; John Mccune Biomedical electrode device
US5648167A (en) 1990-03-29 1997-07-15 Smith & Nephew Plc Adhesive compositions
US5651982A (en) 1994-02-17 1997-07-29 New York Blood Center, Inc. Biologic bioadhesive compositions containing fibrin glue and liposomes, methods of preparation and use
US5665477A (en) 1994-04-04 1997-09-09 Graphic Controls Corporation Hydrogel adhesive for attaching medical device to patient
US5739288A (en) 1992-10-08 1998-04-14 Bristol-Myers Squibb Company Fibrin sealant compositions
US5744545A (en) 1988-11-21 1998-04-28 Collagen Corporation Biocompatible adhesive compositions
US5980515A (en) 1997-12-19 1999-11-09 Irvine Biomedical, Inc. Devices and methods for lead extraction
US6033402A (en) 1998-09-28 2000-03-07 Irvine Biomedical, Inc. Ablation device for lead extraction and methods thereof
US6113948A (en) 1996-05-17 2000-09-05 Quadrant Healthcare Microparticles and their use in wound therapy
US6241692B1 (en) 1998-10-06 2001-06-05 Irvine Biomedical, Inc. Ultrasonic ablation device and methods for lead extraction
US6451025B1 (en) 1996-04-01 2002-09-17 General Surgical Innovations, Inc. Prosthesis and method for deployment within a body lumen
US6485501B1 (en) 2000-08-11 2002-11-26 Cordis Corporation Vascular filter system with guidewire and capture mechanism
US6566649B1 (en) 2000-05-26 2003-05-20 Precision Drilling Technology Services Group Inc. Standoff compensation for nuclear measurements
US6605056B2 (en) 2001-07-11 2003-08-12 Scimed Life Systems, Inc. Conformable balloon
US12080202B2 (en) 2021-08-24 2024-09-03 Lg Display Co., Ltd. Display device, data driving circuit and display driving method

Family Cites Families (88)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US411552A (en) * 1889-09-24 The worcester fire
US682559A (en) * 1901-03-08 1901-09-10 Harry C Mack Bobbin.
US3571815A (en) * 1968-09-19 1971-03-23 John V Somyk Suture ring for heart valve
US3657744A (en) * 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
US3714671A (en) * 1970-11-30 1973-02-06 Cutter Lab Tissue-type heart valve with a graft support ring or stent
US4680031A (en) * 1982-11-29 1987-07-14 Tascon Medical Technology Corporation Heart valve prosthesis
US4626255A (en) * 1983-09-23 1986-12-02 Christian Weinhold Heart valve bioprothesis
US4725274A (en) * 1986-10-24 1988-02-16 Baxter Travenol Laboratories, Inc. Prosthetic heart valve
US4994077A (en) * 1989-04-21 1991-02-19 Dobben Richard L Artificial heart valve for implantation in a blood vessel
EP0474748B1 (fr) * 1989-05-31 1995-01-25 Baxter International Inc. Prothese valvulaire biologique
US5037434A (en) * 1990-04-11 1991-08-06 Carbomedics, Inc. Bioprosthetic heart valve with elastic commissures
US5147391A (en) * 1990-04-11 1992-09-15 Carbomedics, Inc. Bioprosthetic heart valve with semi-permeable commissure posts and deformable leaflets
DK124690D0 (da) * 1990-05-18 1990-05-18 Henning Rud Andersen Klapprotes til implantering i kroppen for erstatning af naturlig klap samt kateter til brug ved implantering af en saadan klapprotese
US5411552A (en) * 1990-05-18 1995-05-02 Andersen; Henning R. Valve prothesis for implantation in the body and a catheter for implanting such valve prothesis
US5370685A (en) * 1991-07-16 1994-12-06 Stanford Surgical Technologies, Inc. Endovascular aortic valve replacement
US5267554A (en) * 1991-11-15 1993-12-07 Wilk Peter J Spreadable laparoscopic retractor and associated method of use
US5163953A (en) * 1992-02-10 1992-11-17 Vince Dennis J Toroidal artificial heart valve stent
US5509900A (en) * 1992-03-02 1996-04-23 Kirkman; Thomas R. Apparatus and method for retaining a catheter in a blood vessel in a fixed position
US6010531A (en) * 1993-02-22 2000-01-04 Heartport, Inc. Less-invasive devices and methods for cardiac valve surgery
EP0667133B1 (fr) * 1993-12-14 2001-03-07 Sante Camilli Valve d'implant percutané pour vaisseaux sanguins
US5752522A (en) * 1995-05-04 1998-05-19 Cardiovascular Concepts, Inc. Lesion diameter measurement catheter and method
US5716417A (en) * 1995-06-07 1998-02-10 St. Jude Medical, Inc. Integral supporting structure for bioprosthetic heart valve
US5769882A (en) * 1995-09-08 1998-06-23 Medtronic, Inc. Methods and apparatus for conformably sealing prostheses within body lumens
DE19536530C1 (de) * 1995-09-29 1996-11-28 Siemens Ag Schnurlos-Telekommunikationssystem mit sichergestellter Interoperabilität von Schnurlos-Telekommunikationsanwendungen, insbesondere einem GAP-spezifischen DECT-System
US6287315B1 (en) * 1995-10-30 2001-09-11 World Medical Manufacturing Corporation Apparatus for delivering an endoluminal prosthesis
US6014137A (en) * 1996-02-27 2000-01-11 Multimedia Adventures Electronic kiosk authoring system
US5855601A (en) 1996-06-21 1999-01-05 The Trustees Of Columbia University In The City Of New York Artificial heart valve and method and device for implanting the same
NL1004827C2 (nl) * 1996-12-18 1998-06-19 Surgical Innovations Vof Inrichting voor het reguleren van de bloedsomloop.
EP0850607A1 (fr) * 1996-12-31 1998-07-01 Cordis Corporation Prothèse de valve pour implantation dans des canaux corporels
US5957949A (en) * 1997-05-01 1999-09-28 World Medical Manufacturing Corp. Percutaneous placement valve stent
US6245102B1 (en) * 1997-05-07 2001-06-12 Iowa-India Investments Company Ltd. Stent, stent graft and stent valve
US5925063A (en) * 1997-09-26 1999-07-20 Khosravi; Farhad Coiled sheet valve, filter or occlusive device and methods of use
US6530952B2 (en) * 1997-12-29 2003-03-11 The Cleveland Clinic Foundation Bioprosthetic cardiovascular valve system
US6159178A (en) 1998-01-23 2000-12-12 Heartport, Inc. Methods and devices for occluding the ascending aorta and maintaining circulation of oxygenated blood in the patient when the patient's heart is arrested
US6102943A (en) * 1998-01-26 2000-08-15 Ave Connaught Endoluminal stents and their manufacture
US6074418A (en) * 1998-04-20 2000-06-13 St. Jude Medical, Inc. Driver tool for heart valve prosthesis fasteners
US7452371B2 (en) * 1999-06-02 2008-11-18 Cook Incorporated Implantable vascular device
US6254636B1 (en) * 1998-06-26 2001-07-03 St. Jude Medical, Inc. Single suture biological tissue aortic stentless valve
US6267781B1 (en) * 1998-08-31 2001-07-31 Quantum Therapeutics Corp. Medical device and methods for treating valvular annulus
US6736845B2 (en) * 1999-01-26 2004-05-18 Edwards Lifesciences Corporation Holder for flexible heart valve
US6558418B2 (en) * 1999-01-26 2003-05-06 Edwards Lifesciences Corporation Flexible heart valve
DK1154738T3 (da) 1999-01-27 2010-07-26 Medtronic Inc Indretninger til hjerteklapindgreb
US6896690B1 (en) * 2000-01-27 2005-05-24 Viacor, Inc. Cardiac valve procedure methods and devices
US6425916B1 (en) * 1999-02-10 2002-07-30 Michi E. Garrison Methods and devices for implanting cardiac valves
US6638717B2 (en) 1999-05-19 2003-10-28 Aventis Pharmaceuticals, Inc. Microarray-based subtractive hybridzation
US6299637B1 (en) * 1999-08-20 2001-10-09 Samuel M. Shaolian Transluminally implantable venous valve
FR2815844B1 (fr) 2000-10-31 2003-01-17 Jacques Seguin Support tubulaire de mise en place, par voie percutanee, d'une valve cardiaque de remplacement
FR2800984B1 (fr) * 1999-11-17 2001-12-14 Jacques Seguin Dispositif de remplacement d'une valve cardiaque par voie percutanee
US7018406B2 (en) * 1999-11-17 2006-03-28 Corevalve Sa Prosthetic valve for transluminal delivery
US6458153B1 (en) * 1999-12-31 2002-10-01 Abps Venture One, Ltd. Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof
NL1014095C2 (nl) * 2000-01-17 2001-07-18 Cornelis Hendrikus Anna Witten Implantaatklep voor implantatie in een bloedvat.
US7749245B2 (en) * 2000-01-27 2010-07-06 Medtronic, Inc. Cardiac valve procedure methods and devices
KR20020082217A (ko) * 2000-01-27 2002-10-30 쓰리에프 쎄러퓨틱스, 인코포레이티드 인공심장판막
DE10010074B4 (de) 2000-02-28 2005-04-14 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Vorrichtung zur Befestigung und Verankerung von Herzklappenprothesen
US6454799B1 (en) 2000-04-06 2002-09-24 Edwards Lifesciences Corporation Minimally-invasive heart valves and methods of use
US7510572B2 (en) * 2000-09-12 2009-03-31 Shlomo Gabbay Implantation system for delivery of a heart valve prosthesis
US6893459B1 (en) * 2000-09-20 2005-05-17 Ample Medical, Inc. Heart valve annulus device and method of using same
WO2002026168A2 (fr) * 2000-09-29 2002-04-04 Tricardia, Llc Dispositif et procede de valvuloplastie veineuse
US6974476B2 (en) * 2003-05-05 2005-12-13 Rex Medical, L.P. Percutaneous aortic valve
US6494909B2 (en) * 2000-12-01 2002-12-17 Prodesco, Inc. Endovascular valve
US6752829B2 (en) * 2001-01-30 2004-06-22 Scimed Life Systems, Inc. Stent with channel(s) for containing and delivering a biologically active material and method for manufacturing the same
NL1017275C2 (nl) 2001-02-02 2002-08-05 Univ Eindhoven Tech Hartklep.
US6503272B2 (en) * 2001-03-21 2003-01-07 Cordis Corporation Stent-based venous valves
US7556646B2 (en) * 2001-09-13 2009-07-07 Edwards Lifesciences Corporation Methods and apparatuses for deploying minimally-invasive heart valves
US6733525B2 (en) * 2001-03-23 2004-05-11 Edwards Lifesciences Corporation Rolled minimally-invasive heart valves and methods of use
WO2002087467A2 (fr) * 2001-04-30 2002-11-07 Thorpe Patricia E Valvule veineuse de remplacement
FR2826863B1 (fr) * 2001-07-04 2003-09-26 Jacques Seguin Ensemble permettant la mise en place d'une valve prothetique dans un conduit corporel
FR2828091B1 (fr) * 2001-07-31 2003-11-21 Seguin Jacques Ensemble permettant la mise en place d'une valve prothetique dans un conduit corporel
US7097659B2 (en) * 2001-09-07 2006-08-29 Medtronic, Inc. Fixation band for affixing a prosthetic heart valve to tissue
US6893460B2 (en) * 2001-10-11 2005-05-17 Percutaneous Valve Technologies Inc. Implantable prosthetic valve
US7192441B2 (en) * 2001-10-16 2007-03-20 Scimed Life Systems, Inc. Aortic artery aneurysm endovascular prosthesis
US6755857B2 (en) * 2001-12-12 2004-06-29 Sulzer Carbomedics Inc. Polymer heart valve with perforated stent and sewing cuff
US20030130729A1 (en) * 2002-01-04 2003-07-10 David Paniagua Percutaneously implantable replacement heart valve device and method of making same
US6716241B2 (en) * 2002-03-05 2004-04-06 John G. Wilder Venous valve and graft combination
US20030199971A1 (en) * 2002-04-23 2003-10-23 Numed, Inc. Biological replacement valve assembly
US6733526B2 (en) * 2002-04-25 2004-05-11 Advanced Medical Optics, Inc. Method of improving adherence and centering of intra-corneal implants on corneal bed
US7331993B2 (en) * 2002-05-03 2008-02-19 The General Hospital Corporation Involuted endovascular valve and method of construction
US7351256B2 (en) 2002-05-10 2008-04-01 Cordis Corporation Frame based unidirectional flow prosthetic implant
WO2003094795A1 (fr) * 2002-05-10 2003-11-20 Cordis Corporation Procede de fabrication de dispositif medical comportant une membrane tubulaire a paroi mince sur un support structural
US20040059412A1 (en) * 2002-09-25 2004-03-25 Lytle Thomas William Heart valve holder
US6682462B1 (en) * 2003-02-21 2004-01-27 Sunny Lee Dual-purpose exerciser operable in pedaling and rowing modes
US7399315B2 (en) * 2003-03-18 2008-07-15 Edwards Lifescience Corporation Minimally-invasive heart valve with cusp positioners
US7530995B2 (en) * 2003-04-17 2009-05-12 3F Therapeutics, Inc. Device for reduction of pressure effects of cardiac tricuspid valve regurgitation
EP2926772A1 (fr) * 2003-04-24 2015-10-07 Cook Medical Technologies LLC Prothèse artificielle de valvule dont la dynamique d'écoulement est améliorée
EP1472995B1 (fr) * 2003-04-30 2008-12-03 Medtronic Vascular, Inc. Système pour réparer des fuites perivasculaires
CA2545874C (fr) 2003-10-06 2012-02-21 3F Therapeutics, Inc. Systeme de remplacement valvulaire minimalement effractif
US7044966B2 (en) 2003-10-06 2006-05-16 3F Therapeutics, Inc. Minimally invasive valve replacement system
US20060025857A1 (en) 2004-04-23 2006-02-02 Bjarne Bergheim Implantable prosthetic valve

Patent Citations (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4768523A (en) 1981-04-29 1988-09-06 Lifecore Biomedical, Inc. Hydrogel adhesive
US5225196A (en) 1983-11-14 1993-07-06 Columbia Laboratories, Inc. Bioadhesive compositions and methods of treatment therewith
US5407671A (en) 1986-07-05 1995-04-18 Behringwerke Aktiengesellschaft One-component tissue adhesive and a process for the production thereof
US5744545A (en) 1988-11-21 1998-04-28 Collagen Corporation Biocompatible adhesive compositions
US5156911A (en) 1989-05-11 1992-10-20 Landec Labs Inc. Skin-activated temperature-sensitive adhesive assemblies
US5387450A (en) 1989-05-11 1995-02-07 Landec Corporation Temperature-activated adhesive assemblies
US5648167A (en) 1990-03-29 1997-07-15 Smith & Nephew Plc Adhesive compositions
US5055046A (en) 1990-09-20 1991-10-08 Isp Investments Inc. Bioadhesive composition
US5066709A (en) 1990-09-20 1991-11-19 Gaf Chemicals Corporation Bioadhesive composition
US5374431A (en) 1990-12-14 1994-12-20 Creative Biomolecules, Inc. Synthetic bioadhesive
US5197973A (en) 1990-12-14 1993-03-30 Creative Biomolecules, Inc. Synthetic bioadhesive
US5578310A (en) 1992-04-23 1996-11-26 Berlex Laboratories Inc. Topical bioadhesive ointment compositions and their use in wound healing
US5739288A (en) 1992-10-08 1998-04-14 Bristol-Myers Squibb Company Fibrin sealant compositions
US5645062A (en) 1993-02-15 1997-07-08 Anderson; John Mccune Biomedical electrode device
US5549904A (en) 1993-06-03 1996-08-27 Orthogene, Inc. Biological adhesive composition and method of promoting adhesion between tissue surfaces
US5651982A (en) 1994-02-17 1997-07-29 New York Blood Center, Inc. Biologic bioadhesive compositions containing fibrin glue and liposomes, methods of preparation and use
US5665477A (en) 1994-04-04 1997-09-09 Graphic Controls Corporation Hydrogel adhesive for attaching medical device to patient
US6451025B1 (en) 1996-04-01 2002-09-17 General Surgical Innovations, Inc. Prosthesis and method for deployment within a body lumen
US6113948A (en) 1996-05-17 2000-09-05 Quadrant Healthcare Microparticles and their use in wound therapy
US5980515A (en) 1997-12-19 1999-11-09 Irvine Biomedical, Inc. Devices and methods for lead extraction
US6033402A (en) 1998-09-28 2000-03-07 Irvine Biomedical, Inc. Ablation device for lead extraction and methods thereof
US6241692B1 (en) 1998-10-06 2001-06-05 Irvine Biomedical, Inc. Ultrasonic ablation device and methods for lead extraction
US6566649B1 (en) 2000-05-26 2003-05-20 Precision Drilling Technology Services Group Inc. Standoff compensation for nuclear measurements
US6485501B1 (en) 2000-08-11 2002-11-26 Cordis Corporation Vascular filter system with guidewire and capture mechanism
US6605056B2 (en) 2001-07-11 2003-08-12 Scimed Life Systems, Inc. Conformable balloon
US12080202B2 (en) 2021-08-24 2024-09-03 Lg Display Co., Ltd. Display device, data driving circuit and display driving method

Cited By (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2789314B1 (fr) 2003-10-06 2018-04-25 Medtronic 3F Therapeutics, Inc. Systeme de remplacement valvulaire minimalement invasif
US11123184B2 (en) 2010-10-05 2021-09-21 Edwards Lifesciences Corporation Prosthetic heart valve
US11628062B2 (en) 2010-10-05 2023-04-18 Edwards Lifesciences Corporation Prosthetic heart valve
US11759320B2 (en) 2010-10-05 2023-09-19 Edwards Lifesciences Corporation Prosthetic heart valve
US11793632B2 (en) 2010-10-05 2023-10-24 Edwards Lifesciences Corporation Prosthetic heart valve
EP3583920B1 (fr) 2011-07-15 2020-06-17 Edwards Lifesciences Corporation Armature de valvule prothétique
US11278400B2 (en) 2011-07-15 2022-03-22 Edwards Lifesciences Corporation Perivalvular sealing for transcatheter heart valve
US11129710B2 (en) 2011-12-09 2021-09-28 Edwards Lifesciences Corporation Prosthetic heart valve having improved commissure supports
US11666434B2 (en) 2011-12-09 2023-06-06 Edwards Lifesciences Corporation Prosthetic heart valve having improved commissure supports
US11690710B2 (en) 2011-12-09 2023-07-04 Edwards Lifesciences Corporation Prosthetic heart valve having improved commissure supports
WO2022159431A1 (fr) * 2021-01-20 2022-07-28 Edwards Lifesciences Corporation Dispositif d'amarrage bi-caval extensible mécaniquement

Also Published As

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US7044966B2 (en) 2006-05-16
US20050075730A1 (en) 2005-04-07
EP2789314A3 (fr) 2014-10-22
US20050075717A1 (en) 2005-04-07
US20050075718A1 (en) 2005-04-07
US20050075724A1 (en) 2005-04-07
US20050075712A1 (en) 2005-04-07
US20050075719A1 (en) 2005-04-07
US20050075726A1 (en) 2005-04-07
US7101396B2 (en) 2006-09-05
EP2789314B1 (fr) 2018-04-25
US20050075713A1 (en) 2005-04-07
US20050075584A1 (en) 2005-04-07
US20050096738A1 (en) 2005-05-05
US20050075728A1 (en) 2005-04-07
US20050075720A1 (en) 2005-04-07
US20050075731A1 (en) 2005-04-07
US20050075729A1 (en) 2005-04-07

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